WO2022170887A1

WO2022170887A1 - Tissue element measurement method and apparatus, and wearable device

Info

Publication number: WO2022170887A1
Application number: PCT/CN2021/143795
Authority: WO
Inventors: 徐可欣; 韩同帅; 姚明飞; 刘雪玉
Original assignee: 先阳科技有限公司
Priority date: 2021-02-11
Filing date: 2021-12-31
Publication date: 2022-08-18
Also published as: KR20230147119A; CN114468993B; US20240130620A1; CN114468993A; US20240225450A9; JP2024513638A; EP4292532A1

Abstract

A tissue element measurement method and apparatus, and a wearable device. Said method comprises: irradiating a measurement area with incident light having a single preset wavelength (S310), each beam of incident light passing through the measurement area and then emitting from at least one emergent position to form at least one beam of emergent light, and the incident light having at least one incident position; acquiring light intensity values corresponding to each beam of emergent light and acquired by M photosensitive surfaces, so as to obtain T output light intensities, the output light intensities being obtained by processing the light intensity values of the emergent light acquired by one or more photosensitive surfaces, each of the photosensitive surfaces being capable of acquiring the light intensity value of the emergent light emitted from the emergent position, corresponding to the photosensitive surface, within a preset anti-shake range, and 1 ≤ T ≤ M (S320); according to at least one output light intensity corresponding to the preset wavelength, determining the concentration of the measured tissue element (S330).

Description

Tissue composition measurement method, device and wearable device

technical field

Embodiments of the present disclosure relate to the technical field of spectral measurement, and more particularly, to a tissue composition measurement method, device, and wearable device.

Background technique

The body fluids of the human body contain a variety of tissue components, such as blood sugar, fat, and white blood cells. The concentration of each tissue component must be within its corresponding concentration range to ensure the healthy operation of the human body. However, for some individuals, because their tissue components are prone to imbalance, that is, the concentration of tissue components is not within the value range, which will lead to diseases, endanger health and even life. Therefore, for such objects, it is necessary to analyze the tissue components. Take real-time measurements.

Because the optical method has the characteristics of rapidity, non-invasiveness and multi-dimensional information, the optical method is usually used to measure the composition in the related art. According to the measurement principle, optical methods mainly include Raman spectroscopy, polarization method, optical coherence tomography, photoacoustic spectroscopy, mid-infrared spectroscopy and near-infrared spectroscopy.

In the process of realizing the concept of the present disclosure, the inventor found that the related art has at least the following problem: it is difficult to obtain reliable measurement results by using the related art.

public content

In view of this, embodiments of the present disclosure provide a tissue composition measurement method, device, and wearable device.

One aspect of the embodiments of the present disclosure provides a method for measuring tissue components, the method comprising: irradiating a measurement area with incident light of a single preset wavelength, wherein each beam of the incident light exits from at least one exit position after passing through the measurement area At least one beam of outgoing light is formed, and the incident position of the above-mentioned incident light includes at least one; the light intensity values corresponding to each beam of the above-mentioned outgoing light collected by the M photosensitive surfaces are obtained, and T output light intensities are obtained, wherein each of the above-mentioned outputs The light intensity is obtained by processing according to the light intensity value of the outgoing light collected by one or more of the above-mentioned photosensitive surfaces. The light intensity value of the outgoing outgoing light is 1≤T≤M; and, according to at least one output light intensity corresponding to the preset wavelength, the concentration of the measured tissue component is determined.

Another aspect of the embodiments of the present disclosure provides a tissue composition measurement device, the device includes: a light source module for irradiating a measurement area with incident light of a single preset wavelength, wherein after each beam of the incident light passes through the measurement area At least one beam of outgoing light is emitted from at least one outgoing position, and the incident position of the incident light includes at least one; a collection module, the collection module includes M photosensitive surfaces, and each of the photosensitive surfaces can collect a corresponding photosensitive surface. The light intensity value of the outgoing light emitted from the outgoing position within the preset anti-shake range, the above-mentioned acquisition module is used to obtain the light intensity value corresponding to each beam of the above-mentioned outgoing light collected by the above-mentioned M photosensitive surfaces, and obtain T outputs Light intensity, wherein each of the above-mentioned output light intensity is obtained by processing according to the light intensity value of the outgoing light collected by one or more of the above-mentioned photosensitive surfaces, 1≤T≤M; At least one output light intensity corresponding to the wavelength is set to determine the concentration of the measured tissue component.

Another aspect of an embodiment of the present disclosure provides a wearable device including the tissue composition measurement device as described above.

Description of drawings

The above and other objects, features and advantages of the present disclosure will become more apparent from the following description of embodiments of the present disclosure with reference to the accompanying drawings, in which:

1 schematically shows a schematic diagram of using a photosensitive surface with a small area to receive outgoing light when jitter occurs according to an embodiment of the present disclosure;

FIG. 2 schematically shows a schematic diagram of using a photosensitive surface with a larger area to receive outgoing light when jitter occurs according to an embodiment of the present disclosure;

FIG. 3 schematically shows a flow chart of a tissue composition measurement method according to an embodiment of the present disclosure;

FIG. 4 schematically shows a schematic diagram of a measurement result obtained by a Monte Carlo simulation method according to an embodiment of the present disclosure;

FIG. 5 schematically shows a schematic diagram of realizing the positioning of the measurement area based on an optical method according to an embodiment of the present disclosure;

FIG. 6 schematically shows another schematic diagram of realizing the positioning of the measurement area based on an optical method according to an embodiment of the present disclosure;

FIG. 7 schematically shows a schematic diagram of realizing the positioning of the measurement area based on an image matching method according to an embodiment of the present disclosure;

FIG. 8 schematically shows a schematic diagram of realizing the positioning of the measurement area based on another image matching method according to an embodiment of the present disclosure;

FIG. 9 schematically shows a schematic diagram of positioning the measurement area implemented by an imaging method according to an embodiment of the present disclosure;

FIG. 10 schematically shows a schematic diagram of implementing positioning of a measurement area based on another imaging method according to an embodiment of the present disclosure;

FIG. 11 schematically shows a schematic diagram of realizing the positioning of the measurement posture based on an optical method according to an embodiment of the present disclosure;

FIG. 12 schematically shows a schematic diagram of realizing the positioning of the measurement posture by an image matching method according to an embodiment of the present disclosure;

Fig. 13 schematically shows a schematic diagram of realizing the positioning of the measurement posture based on an imaging method according to an embodiment of the present disclosure;

FIG. 14 schematically shows a schematic diagram of a differential measurement according to an embodiment of the present disclosure;

15 schematically shows a schematic diagram of a ring-shaped photosensitive surface according to an embodiment of the present disclosure;

16 schematically shows a schematic diagram of a fan ring photosensitive surface according to an embodiment of the present disclosure;

17 schematically shows a schematic diagram of a circular photosensitive surface according to an embodiment of the present disclosure;

FIG. 18 schematically shows a schematic diagram of a square photosensitive surface according to an embodiment of the present disclosure;

19 schematically shows a schematic diagram of setting a mask plate on an initial photosensitive surface to obtain a photosensitive surface according to an embodiment of the present disclosure;

FIG. 20 schematically shows a block diagram of a tissue composition measurement device according to an embodiment of the present disclosure;

FIG. 21 schematically shows a block diagram of another tissue composition measurement device according to an embodiment of the present disclosure;

FIG. 22 schematically shows a schematic diagram of the positional relationship between a fixing part and a measuring probe according to an embodiment of the present disclosure;

FIG. 23 schematically shows a schematic structural diagram of a fixing part according to an embodiment of the present disclosure;

Fig. 24 schematically shows a schematic diagram of a first fitting according to an embodiment of the present disclosure;

FIG. 25 schematically shows a schematic diagram of another first fitting according to an embodiment of the present disclosure;

Fig. 26 schematically shows a schematic diagram of a region positioning part according to an embodiment of the present disclosure;

FIG. 27 schematically shows a schematic diagram of another area positioning part according to an embodiment of the present disclosure;

FIG. 28 schematically shows a schematic diagram of a first image acquisition part according to an embodiment of the present disclosure;

FIG. 29 schematically shows a schematic diagram of a first posture positioning part according to an embodiment of the present disclosure;

FIG. 30 schematically shows a schematic diagram of another first posture positioning part according to an embodiment of the present disclosure;

FIG. 31 schematically shows a schematic diagram of a third image acquisition part according to an embodiment of the present disclosure;

FIG. 32 schematically shows a schematic diagram of a measurement posture and measurement area positioning according to an embodiment of the present disclosure;

FIG. 33 schematically shows another schematic diagram of measurement posture and measurement area positioning according to an embodiment of the present disclosure;

FIG. 34 schematically shows a schematic diagram of anode electrical connection of different photosensitive surfaces according to an embodiment of the present disclosure;

FIG. 35 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of a glove according to an embodiment of the present disclosure;

FIG. 36 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of another glove according to an embodiment of the present disclosure;

37 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of a wristband according to an embodiment of the present disclosure;

FIG. 38 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of another wristband according to an embodiment of the present disclosure;

FIG. 39 schematically shows a schematic diagram of a stereoscopic photosensitive surface for arm measurement according to an embodiment of the present disclosure;

FIG. 40 schematically shows a schematic diagram of setting a first sleeve on a measuring probe according to an embodiment of the present disclosure;

41 schematically shows a schematic diagram of disposing a second sleeve outside the target area of a first sleeve according to an embodiment of the present disclosure;

FIG. 42 schematically shows a schematic diagram of a photosensitive surface receiving outgoing light without an index matching material being filled according to an embodiment of the present disclosure;

FIG. 43 schematically shows a schematic diagram of a photosensitive surface receiving outgoing light under the condition of filling with an index matching material according to an embodiment of the present disclosure;

FIG. 44 schematically shows another schematic diagram of the photosensitive surface receiving the outgoing light under the condition of filling the index matching material according to an embodiment of the present disclosure;

Figure 45 schematically shows a schematic diagram of a diffusion measurement according to an embodiment of the present disclosure;

FIG. 46 schematically shows a schematic diagram of a wearable device according to an embodiment of the present disclosure;

FIG. 47 schematically shows a schematic diagram of an assembling process of a wearable device according to an embodiment of the present disclosure;

FIG. 48 schematically shows a method according to an embodiment of the present disclosure, under the condition that the wearable device is consistent with the skin shaking law, the average optical length of the outgoing light received by the measurement probe is kept at a preset optical length during the skin shaking process A schematic diagram of the range;

FIG. 49 schematically shows the average optical path length of the outgoing light received by the measurement probe under the condition that the movement amplitude of the skin at the measurement area is less than or equal to the movement amplitude threshold value in the case where the wearable device according to the embodiment of the present disclosure is jittered on the skin Schematic diagram of keeping within the preset optical path range during the process;

Fig. 50 schematically shows a schematic diagram of synchronously realizing the positioning of the measurement area and the positioning of the measurement posture based on an optical method according to an embodiment of the present disclosure;

FIG. 51 schematically shows a schematic diagram of the variation of the differential signal obtained by measuring a standard reflective plate according to an embodiment of the present disclosure as a function of the measurement duration;

Figure 52 schematically shows a schematic diagram of the variation of the differential signal obtained by measuring the extension side of the forearm of the subject under a steady state of blood glucose concentration with the measurement duration according to an embodiment of the present disclosure;

Figure 53 schematically shows a schematic diagram of the results of a single sugar loading experiment using the OGTT method according to an embodiment of the present disclosure;

Figure 54 schematically shows a schematic diagram of the relationship between the variation of the differential signal and the true value of blood glucose according to an embodiment of the present disclosure;

Figure 55 schematically shows a schematic diagram of the results of a double sugar loading experiment using the MTT method according to an embodiment of the present disclosure; and

FIG. 56 schematically shows a schematic diagram of a relationship between a predicted blood glucose value and a true blood glucose value according to an embodiment of the present disclosure.

Detailed ways

Hereinafter, embodiments of the present disclosure will be described with reference to the accompanying drawings. It should be understood, however, that these descriptions are exemplary only, and are not intended to limit the scope of the present disclosure. In the following detailed description, for convenience of explanation, numerous specific details are set forth in order to provide a thorough understanding of the embodiments of the present disclosure. It will be apparent, however, that one or more embodiments may be practiced without these specific details. Also, in the following description, descriptions of well-known structures and techniques are omitted to avoid unnecessarily obscuring the concepts of the present disclosure.

The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the present disclosure. The terms "comprising", "comprising" and the like as used herein indicate the presence of stated features, steps, operations and/or components, but do not preclude the presence or addition of one or more other features, steps, operations or components.

All terms (including technical and scientific terms) used herein have the meaning as commonly understood by one of ordinary skill in the art, unless otherwise defined. It should be noted that terms used herein should be construed to have meanings consistent with the context of the present specification and should not be construed in an idealized or overly rigid manner.

Where expressions like "at least one of A, B, and C, etc.," are used, they should generally be interpreted in accordance with the meaning of the expression as commonly understood by those skilled in the art (eg, "has A, B, and C") At least one of the "systems" shall include, but not be limited to, systems with A alone, B alone, C alone, A and B, A and C, B and C, and/or A, B, C, etc. ). Where expressions like "at least one of A, B, or C, etc.," are used, they should generally be interpreted in accordance with the meaning of the expression as commonly understood by those skilled in the art (eg, "has A, B, or C, etc." At least one of the "systems" shall include, but not be limited to, systems with A alone, B alone, C alone, A and B, A and C, B and C, and/or A, B, C, etc. ).

The research on the measurement of living tissue components based on optical methods has experienced nearly 50 years of development. Although a large number of scientific research institutes and companies have invested great research enthusiasm in this field, the absorption of the measured tissue components is usually higher than that of the measured tissue components. Weak, the variation range of the measured tissue component concentration of the measured object itself is usually not large, therefore, the measured tissue component signal is usually weak, and interference such as changes in measurement conditions will easily overwhelm the weak measured tissue component signal, while No solution has yet emerged to achieve reliable measurement of tissue composition in vivo. Therefore, the measurement of tissue composition in vivo is a world problem that needs to be solved urgently. Among them, the tissue components can include blood sugar, fat and white blood cells. The measured tissue component signal represents the output light intensity change caused by the concentration change of the measured tissue component. The measurement conditions can be understood as conditions affecting the transmission path of light. The measurement conditions may include controllable measurement conditions and uncontrollable measurement conditions. The controllable measurement conditions refer to the measurement conditions that can be controlled to remain within a preset variation range (ie, remain unchanged or substantially unchanged) by using an effective control method during each tissue component measurement process. Uncontrollable measurement conditions are measurement conditions with unpredictable and uncontrollable characteristics. Controllable measurement conditions may include temperature, pressure, measurement area, measurement posture, and the like. Uncontrollable measurement conditions may include physiological background changes and measurement device drift, among others.

In the process of realizing the concept of the present disclosure, the inventors found that the main reason why it is difficult to obtain reliable measurement results by using related technologies is that.

The inventors found that if only the intensity distribution of the light spot irradiated by the incident light to the measurement area is changed under the condition that other conditions remain unchanged, the obtained measurement results are different. If the measurement results obtained by setting the photosensitive surface close to the blood vessel are compared with the measurement results obtained by setting the same photosensitive surface far away from the blood vessel under the condition that other conditions remain unchanged, the measurement results obtained by setting the photosensitive surface away from the blood vessel are better than those obtained by setting the photosensitive surface away from the blood vessel. Set the resulting measurement. Wherein, the measurement result can be characterized by the relative variation of the light intensity value of the light received by the photosensitive surface and the standard deviation of the light intensity value. When studying the reasons for the different measurement results, it was found that changing the intensity distribution of the light spot irradiated by the incident light to the measurement area can reflect the randomness of the light source irradiation, the distance from the blood vessel can reflect the strength of the pulse beat, and the randomness of the light source irradiation and the pulse Jitter is a source of jitter. Thus, it was found that one of the reasons for the difficulty in obtaining reliable measurement results is jitter.

Based on the research on jitter, it is found that according to the source that causes jitter, it can be divided into internal sources and external sources. Among them, the internal source can include not only the pulse beat, but also the physiological background variation. In addition to the randomness of the illumination of the light source, the external source can also include the uncertainty of the transmission of the incident light itself. The randomness of the light source illumination can be reflected by the intensity distribution of the light spot illuminated by the incident light to the measurement area. It was found that both the jitter caused by internal sources and the jitter caused by external sources will affect the transmission path of light in the tissue, thereby affecting the intensity distribution of the outgoing light on the measurement area.

In order to solve the problem of low reliability of measurement results caused by jitter, the inventors found that a photosensitive surface with a large area (ie, a large-area photosensitive surface) can be used to collect the light intensity value of the outgoing light, so as to effectively suppress the effect of jitter on the adverse effects on measurement results. That is to say, the large-area photosensitive surface can effectively suppress the adverse effects caused by jitter. The so-called "large-area photosensitive surface" can be understood as the area of the photosensitive surface that enables the photosensitive surface to collect the outgoing light from the exit position within the preset anti-shake range. light intensity value. The area of the large-area photosensitive surface is continuous, and the large-area photosensitive surface is made of photosensitive materials, which is different from single-point fiber receiving and multiple single-fiber joint receiving. The following will specifically explain why the scheme of collecting the output light intensity of the outgoing light with a large-area photosensitive surface can effectively suppress the adverse effect of jitter on the measurement results.

Since the large-area photosensitive surface can increase the ratio of the area of the photosensitive surface that can stably receive the outgoing light to the area of the photosensitive surface, the stability of receiving outgoing light can be improved, and the intensity distribution of the outgoing light caused by jitter can be reduced. adverse effects of changes, thereby increasing the reliability of the measurement results. Among them, the stability can be characterized by the relative change of the light intensity value of the light received by the photosensitive surface or the standard deviation of the light intensity value. The smaller the relative change of the light intensity value, the higher the stability, and the higher the standard deviation of the light intensity value. Smaller, the higher the stability.

Illustratively, the jitter caused by pulse beating is taken as an example for description. Pulse beat can be reflected by the state of blood vessels. FIG. 1 schematically shows a schematic diagram of using a photosensitive surface with a small area to receive outgoing light when jitter occurs according to an embodiment of the present disclosure. FIG. 2 schematically shows a schematic diagram of using a photosensitive surface with a larger area to receive outgoing light when jitter occurs according to an embodiment of the present disclosure. The same jitter occurs in Figures 1 and 2. The area of the photosensitive surface A in FIG. 1 is smaller than the area of the photosensitive surface B in FIG. 2 . Both the photosensitive surface A and the photosensitive surface B are square photosensitive surfaces. In FIGS. 1 and 2 , the vascular state 1 represents the vasoconstriction state, the vascular state 2 represents the vasodilation state, the skin state 1 represents the skin state corresponding to the vascular state 1 , and the skin state 2 represents the skin state corresponding to the vascular state 2 . Skin state 1 to skin state 2 embody jitter.

Compare measurements obtained with photosensitive surfaces of different areas under the same jitter. The measurement result is characterized by the relative variation of the light intensity value or the standard deviation of the light intensity value when the photosensitive surface receives the outgoing light within a preset time period. Wherein, the relative change of the light intensity value can be determined by the following methods: calculating the difference between the maximum light intensity value and the minimum light intensity value within the preset time period, calculating the average value of the outgoing values within the preset time period, and calculating the difference The ratio of the value to the average value, and the ratio is used as the relative change of the light intensity value. The preset time period may be a pulse period.

The measurement results also show that no matter whether the relative variation of the light intensity value of the outgoing light received by the photosensitive surface is used to characterize the measurement result, or the standard deviation of the light intensity value of the outgoing light received by the photosensitive surface is used to characterize the measurement result, the measurement results obtained by the photosensitive surface B are all the same. Better than measurements obtained with photosensitive surface A.

Since the area of the photosensitive surface B is larger than that of the photosensitive surface A, it can be explained that the large-area photosensitive surface can improve the stability of receiving the outgoing light, thereby reducing the adverse effects of changes in the intensity distribution of the outgoing light caused by jitter, thereby improving the measurement accuracy.

In addition, since the output light intensity of the outgoing light is relatively weak, the change in the output light intensity caused by the concentration change of the measured tissue component is also relatively weak, and the method of receiving the outgoing light adopted in the related art has a low efficiency of the outgoing light received. , therefore, the signal-to-noise ratio of the received output light intensity is relatively low, resulting in low reliability of the measurement results. The large-area photosensitive surface of the embodiment of the present disclosure can improve the signal-to-noise ratio of the output light intensity, thereby improving the reliability of the measurement result. This is because the large-area photosensitive surface can receive a wide range of outgoing light and improve the efficiency of receiving outgoing light, thereby improving the signal-to-noise ratio of the output light intensity and improving the reliability of the measurement results.

It should be noted that, the large-area photosensitive surface described in the embodiments of the present disclosure can achieve higher received and outgoing light when the distance from the surface of the measurement area is small, that is, when it is close to the surface of the measurement area stability and efficiency. This cannot be achieved by single-point fiber receiving and multiple single-fiber joint receiving because, first, it is limited by the numerical aperture of the fiber; second, it is limited by the state change of the fiber. The state of the optical fiber is easily affected by the environment, and its change has a great influence on the stability of receiving outgoing light.

It should also be noted that, generally, in order to improve the signal-to-noise ratio of the output light intensity, a large-area photosensitive surface can be used. In other words, the large-area photosensitive surface usually plays a role in improving the signal-to-noise ratio of the output light intensity, which is different from the main role played by the large-area photosensitive surface in the embodiment of the present disclosure. In the embodiment of the present disclosure, The role of the large-area photosensitive surface is to effectively suppress jitter.

At the same time, in the process of realizing the concept of the present disclosure, the inventors found that in the related art, multivariate analysis method is usually used to process multi-wavelength spectral data, that is, the multivariate analysis method is used to establish the relationship between the optical signal and the true value of the measured tissue component concentration The established mathematical model is used to predict the concentration of the measured tissue component, so that the measured tissue component signal can be obtained indirectly. And it is believed that the measurement of living tissue components can only be achieved by using multivariate analysis methods. This is because tissue components and physical states (such as temperature and pressure, etc.) have characteristic absorption in preset frequency bands. Potential tool for interference correction in measurements. Wherein, the preset wavelength band may include visible-near infrared wavelength band. Given the above-mentioned properties of multivariate analysis methods, some researchers are overconfident in the reliability of multivariate analysis methods. Therefore, the direction of improvement in the related art is also developed along the multivariate analysis method.

However, the above methods have the following problems. The signal changes caused by changes in measurement conditions are usually much larger than those caused by changes in the concentration of the measured tissue components. Therefore, the measurement results obtained by the multivariate analysis method are likely to be different from the measured tissue components. There is an accidental correlation between signal changes caused by external interference (such as physiological background interference), which in turn leads to the result of this indirect extraction of the measured tissue component signal may be a false correlation result.

Since the measurement results obtained by the above methods may be pseudo-correlation results, they cannot directly prove that the obtained measured tissue component signal is the real measured tissue component signal, and therefore, cannot directly prove that the measurement of living tissue component is feasible. Therefore, the reliability of the measurement results is not high.

The direct acquisition of the real measured tissue composition signal is a prerequisite for the realization of living tissue composition measurement. In order to ensure that the real measured tissue composition signal can be obtained to improve the reliability of the measurement result, the embodiment of the present disclosure proposes a solution of using a single preset wavelength combined with a large-area photosensitive surface to measure the tissue composition of the living body.

At the same time, in order to realize the application of the living tissue composition measurement device and the wearable device provided with the living tissue composition measurement device, it is necessary to make the volume of the device and the device as small as possible, and the power consumption is as small as possible, which is convenient for practical use. When a single preset wavelength is used, the volume and structural complexity of the light source module can be reduced, thereby reducing the volume and structural complexity of devices and equipment, facilitating portable measurement, and reducing the capacity requirement for the power module, thereby reducing the cost of production. In addition, the amount of data processing can also be reduced.

The following will be described with reference to specific embodiments.

FIG. 3 schematically shows a flow chart of a tissue composition measurement method according to an embodiment of the present disclosure.

As shown in FIG. 3, the method includes operations S310-S330.

In operation S310, the measurement area is irradiated with a single preset wavelength of incident light, wherein each incident light passes through the measurement area and is emitted from at least one exit position to form at least one exit light, and the incident light incident position includes at least one.

According to the embodiments of the present disclosure, since different measurement sites have different skin characteristics, which may include smoothness, presence or absence of hair, flatness, skin thickness and softness, etc., it is necessary to select the measurement according to the actual situation, such as the structure of the measurement probe. suitable measurement site. The measurement site may include at least one of fingers, palms, arms, foreheads, and earlobes. The measurement area may be an area on the measurement site.

According to an embodiment of the present disclosure, the single preset wavelength may be a wavelength sensitive to the measured tissue composition. The band to which a single preset wavelength belongs may include an ultraviolet band, a visible light band, a near-infrared band, a mid-infrared band, or a far-infrared band. Exemplarily, if the measured tissue component is blood sugar, correspondingly, the single preset wavelength can be a wavelength sensitive to blood sugar, and specifically can be 1550 nm or 1609 nm. Incident light can be collimated or non-collimated. The incident position of the incident light may be one or more.

In operation S320, light intensity values corresponding to each outgoing light collected by the M photosensitive surfaces are acquired, and T output light intensities are obtained, wherein each output light intensity is an outgoing light collected according to one or more photosensitive surfaces Each photosensitive surface can collect the light intensity value of the outgoing light emitted from the outgoing position within the preset anti-shake range corresponding to the photosensitive surface, 1≤T≤M.

According to the embodiments of the present disclosure, in order to improve the reliability of the measurement results, it is necessary to try to ensure that each photosensitive surface can collect the light intensity value of the outgoing light emitted from the outgoing position within the preset anti-shake range corresponding to the photosensitive surface , which requires the area of the photosensitive surface to be as large as possible. Each photosensitive surface has a corresponding preset anti-shake range, and the preset anti-shake ranges of different photosensitive surfaces are the same or different. In the following, it will be explained from three aspects that the larger the area of the photosensitive surface, the better the effect of suppressing jitter. It is preset that the area of the photosensitive surface A is smaller than the area of the photosensitive surface B. Both the photosensitive surface A and the photosensitive surface B are square photosensitive surfaces.

One is to suppress the jitter caused by the pulse beat. The photosensitive surface A and the photosensitive surface B are respectively set at the same position on the measurement area, which is a position close to the blood vessel. Under other conditions being the same, compare the measurement results obtained with the photosensitive surface A and the photosensitive surface B, wherein the measurement results use the relative change or the light intensity value of the light intensity value of the outgoing light received by the photosensitive surface during one pulsation period. standard deviation representation. The calculation method of the relative change of the light intensity value is as described above, and will not be repeated here. It is found that the relative variation of the light intensity value of the outgoing light received by the photosensitive surface B is smaller than the relative change of the light intensity value of the outgoing light received by the photosensitive surface A, and the standard deviation of the light intensity value of the outgoing light received by the photosensitive surface B is smaller than that received by the photosensitive surface A. The standard deviation of the light intensity values of the incident light. From this, it can be concluded that whether the measurement result is characterized by the relative change of the light intensity value of the outgoing light received by the photosensitive surface, or the standard deviation of the light intensity value of the outgoing light received by the photosensitive surface is used to characterize the measurement result, the measurement obtained by the photosensitive surface B is used to characterize the measurement result. The results are all better than those obtained with the photosensitive surface A.

Since the measurement results obtained by using the photosensitive surface B are better than those obtained by using the photosensitive surface A, and the area of the photosensitive surface B is larger than the area of the photosensitive surface A, it can be said that the larger the area of the photosensitive surface, the more effective it is to suppress the pulse beat. The better the dithering effect.

Second, the jitter caused by the change in the intensity distribution of the light spot irradiated to the measurement area by the incident light is suppressed. Under the condition that other conditions remain unchanged, only the intensity distribution of the light spot irradiated by the incident light to the measurement area is changed. Compare the measurement results obtained by using the photosensitive surface A and using the photosensitive surface B, wherein the measurement results are characterized by the relative variation of the light intensity value or the standard deviation of the light intensity value received by the photosensitive surface during a preset time period. The calculation method of the relative change of the light intensity value is as described above, and will not be repeated here. It is found that the variation of the light intensity value of the outgoing light received by the photosensitive surface B is smaller than the variation of the light intensity value of the outgoing light received by the photosensitive surface A, and the standard deviation of the light intensity value of the outgoing light received by the photosensitive surface B is smaller than that of the outgoing light received by the photosensitive surface A. Standard deviation of light intensity values. From this, it can be concluded that whether the relative change of the light intensity value of the light received by the photosensitive surface is used to characterize the measurement result, or the standard deviation of the light intensity value of the light received by the photosensitive surface is used to characterize the measurement result, and the measurement obtained by the photosensitive surface B is used. The results are all better than the measurement results obtained with the photosensitive surface A.

Since the measurement results obtained by using the photosensitive surface B are better than those obtained by using the photosensitive surface A, and the area of the photosensitive surface B is larger than the area of the photosensitive surface A, it can be said that the larger the area of the photosensitive surface, the inhibition of the incident light irradiation to the The better the effect of jitter caused by changes in the intensity distribution of the light spot in the measurement area.

Third, the jitter caused by the uncertainty of the transmission of the incident light itself is suppressed. The Monte Carlo simulation method was used. The center of incident light with a photon number of 10 ¹⁵ is incident, and the photosensitive surface A and the photosensitive surface B are respectively set at 2.4 mm from the center of the incident light, and the number of simulations is 22. Compare the measurement results obtained by using the photosensitive surface A and the photosensitive surface B. The measurement results are characterized by the standard deviation of the number of emitted photons per unit area. The smaller the standard deviation of the number of emitted photons per unit area, the better the suppression effect. FIG. 4 is a schematic diagram of a measurement result obtained by a Monte Carlo simulation method according to an embodiment of the present disclosure. It is found that the standard deviation of the number of emitted photons per unit area corresponding to the photosensitive surface B is smaller than the standard deviation of the number of emitted photons per unit area corresponding to the photosensitive surface A. That is, the measurement results obtained using the photosensitive surface B are better than the measurement results obtained using the photosensitive surface A.

Since the measurement results obtained by using the photosensitive surface B are better than the measurement results obtained by using the photosensitive surface A, and the area of the photosensitive surface B is larger than that of the photosensitive surface A, it can be explained that the larger the area of the photosensitive surface is, the greater the area of the photosensitive surface can be The better the effect of jitter caused by the uncertainty of the transmission.

Through the examples of the above three aspects, it is explained that the larger the area of the photosensitive surface, the better the effect of suppressing the adverse effects of jitter on the measurement results.

According to an embodiment of the present disclosure, each photosensitive surface may be set as a ring-shaped photosensitive surface or a non-annular photosensitive surface, wherein the non-annular photosensitive surface may include a fan-shaped photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a Polygonal photosensitive surface. The polygonal photosensitive surface may include a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

According to the embodiment of the present disclosure, each of the M photosensitive surfaces can be used alone, partially combined, or all combined, and the combined use means outputting one output light intensity. In the embodiments of the present disclosure, a photosensitive surface for outputting one output light intensity is referred to as a similar photosensitive surface, and a similar photosensitive surface may include one or more photosensitive surfaces. Wherein, the condition for the combined use of different photosensitive surfaces may be that the average optical length of the outgoing light received by each photosensitive surface is within the range of the average optical length. The average optical path range may be a range consisting of greater than or equal to the first average optical path threshold and less than or equal to the second average optical path threshold. The first average optical path threshold and the second average optical path threshold may be determined according to the optical path average value and the optical path variation amplitude. The average optical path length is an average value calculated from the average optical path lengths of the outgoing light received by each photosensitive surface of the same type of photosensitive surface. Exemplarily, if the average optical path length is a, and the optical path variation range is ±30%, the first average optical path threshold may be 0.7a, and the second average optical path threshold may be 1.3a.

The average optical path length will be described below. The transmission path of light in the tissue can be represented by the optical path and the penetration depth, where the optical path is used to represent the total distance of light transmission in the tissue, and the penetration depth is used to represent the maximum longitudinal distance that the light can reach in the tissue . For a determined source-to-detection distance, the average optical path length is used to represent the average of the optical path lengths of light in the tissue. The probability distribution function of the optical path can be understood as a function of the source-detection distance and tissue optical parameters, wherein the source-detection distance represents the radial distance between the center of the incident light and the center of the photosensitive surface. Correspondingly, in mathematical expression, the average optical path can be understood as a function of the source-probe distance and tissue optical parameters, wherein the tissue optical parameters can include absorption coefficient, scattering coefficient and anisotropy factor. Factors affecting the average optical path may include absorption coefficient, scattering coefficient, anisotropy factor, and source-detection distance.

According to an embodiment of the present disclosure, the same type of photosensitive surface may be an annular photosensitive surface or a non-annular photosensitive surface. The same type of photosensitive surface is an annular photosensitive surface, which may be included in the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent annular photosensitive surface. When the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a ring-shaped photosensitive surface formed by combining the multiple photosensitive surfaces. The same type of photosensitive surface is a non-annular photosensitive surface, which may be included in the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed according to the combination of the multiple photosensitive surfaces.

In operation S330, the concentration of the measured tissue component is determined according to at least one output light intensity corresponding to the preset wavelength.

According to an embodiment of the present disclosure, after obtaining at least one output light intensity corresponding to the preset wavelength, the interference suppression method may be used to process the at least one output light intensity corresponding to the preset wavelength to determine the concentration of the measured tissue component. Wherein, the interference suppression method may include a differential measurement method. The differential measurement method may include a time differential measurement method or a position differential measurement method. Alternatively, at least one output light intensity can also be processed using a non-differential measurement method to determine the concentration of the measured tissue component. Each output light intensity may include diffusely scattered light intensity or diffusely transmitted light intensity.

According to the technical solutions of the embodiments of the present disclosure, the photosensitive surface can collect the light intensity value of the outgoing light emitted from the outgoing position within the corresponding preset anti-disturbance range. The ratio of the area of stably receiving the outgoing light to the area of the photosensitive surface, therefore, improves the stability of receiving outgoing light, thereby reducing the adverse effects of changes in the intensity distribution of the outgoing light caused by jitter, thereby improving the accuracy of the measurement results. reliability. At the same time, a single preset wavelength is used in combination with the photosensitive surface with the above characteristics to measure the tissue composition, and the real measured tissue composition signal is directly obtained. Using a single preset wavelength for tissue composition measurement reduces the volume and structural complexity of the light source module, thereby reducing the volume and structural complexity of devices and equipment, facilitating portable measurement, reducing the capacity requirements for power modules, and reducing cost of production. In addition, the amount of data processing is also reduced.

According to an embodiment of the present disclosure, the ratio of the average optical length of the outgoing light received by each photosensitive surface in the target tissue layer to the total optical length is greater than or equal to the ratio threshold, where the total optical length is the transmission of the outgoing light in the measurement area. total distance.

According to the embodiment of the present disclosure, the tissue model of the measured object is usually a layered structure, that is, it can be divided into one or more layers. Different tissue layers carry different information on the measured tissue components. In order to improve the reliability of the measurement results, it is necessary to make the transmission path of the outgoing light mainly pass through the tissue layers with rich information on the measured tissue components. The target tissue layer can be understood as the tissue layer that carries the information of the measured tissue components, or the tissue layer that is the main source of the measured tissue components. The following description will be given by taking the measured object as the human body and the measured tissue component as blood glucose as an example.

The human skin tissue model can be understood as a three-layer model, from outside to inside are the epidermis, dermis and subcutaneous fat layer. Among them, the epidermis contains a small amount of tissue fluid and does not contain plasma and lymph. The dermis contains a large amount of tissue fluid, and because of the abundant capillaries, it also contains a large amount of plasma and a small amount of lymph. The subcutaneous fat layer contains a small amount of cellular fluid, and because of the existence of blood vessels such as veins and arteries, it contains a large amount of plasma and a small amount of lymph fluid. It can be seen that the information of the measured tissue components carried by different tissue layers is different.

Since the epidermis contains a small amount of tissue fluid, the epidermis is not a suitable source of blood glucose information. Although the subcutaneous fat layer contains a large amount of plasma and a relatively small amount of interstitial fluid, it is also not a suitable source of blood glucose information due to the limited depth of penetration of incident light. Since the dermis layer contains abundant capillaries and a large amount of tissue fluid, and incident light can easily reach the dermis layer, the dermis layer can be the main source of blood glucose information. Correspondingly, the target tissue layer may be the dermis layer.

According to the embodiments of the present disclosure, the average optical path length of the outgoing light in each tissue layer can be determined according to the optical path length and the penetration depth.

In order to ensure that the transmission path of the outgoing light is mainly the outgoing light passing through the target tissue layer, it is necessary to make the ratio of the average optical length of the outgoing light received by each photosensitive surface in the target tissue layer to the total optical length greater than or equal to the proportional threshold. The total optical path may be the total distance traveled by the outgoing light in the measurement area, that is, the total distance traveled by the incident light from entering the measurement area, traveling in the measurement area until reaching the outgoing position. Among them, the proportional threshold is related to the source-detection distance between the center of the photosensitive surface and the center of the incident light and the tissue optical parameters.

It should be noted that, since the embodiments of the present disclosure limit the ratio of the average optical path length of the outgoing light received by the photosensitive surface in the target tissue layer to the total optical path length, the area of the photosensitive surface in the embodiments of the present disclosure cannot exceed Large, which is a large area within an area range.

According to the embodiment of the present disclosure, the total area of the same type of photosensitive surface is determined according to the tissue structure features in the measurement area, wherein the same type of photosensitive surface includes one or more photosensitive surfaces, and the same type of photosensitive surface is used to output one output light intensity.

According to an embodiment of the present disclosure, the total area of the photosensitive surfaces of the same type may be determined according to the tissue structure characteristics in the measurement area. Among them, the organizational structure feature can be understood as the structural feature possessed by the measurement area.

Exemplarily, if the measurement area is the area where three blood vessels intersect, if the same photosensitive surface is set in the area where the three blood vessels intersect, the total area of the same photosensitive surface is limited by the area where the three blood vessels intersect, that is, the same photosensitive surface. The total area needs to be determined based on the area of the area where the three vessels intersect.

Another example is that the measurement area is the area where the finger is located. If the same photosensitive surface is set in the area where the finger is located, the total area of the same photosensitive surface is limited by the area where the finger is located, that is, the total area of the same photosensitive surface needs to be based on the area where the finger is located. area is determined.

It should be noted that, since the area of the photosensitive surface in the embodiment of the present disclosure can be determined according to the characteristics of the tissue structure, and generally the area determined according to the characteristics of the tissue structure cannot be too large, therefore, the area of the photosensitive surface in the embodiment of the present disclosure cannot be too large, It is a large area within an area.

According to an embodiment of the present disclosure, the ratio of the area of each photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold.

According to the embodiments of the present disclosure, in order to reduce the influence of the uncertainty of incident light transmission, randomness of light source, physiological background variation, and jitter caused by pulse beating on the distribution of outgoing light on the measurement area, the area of the photosensitive surface can be The reason is that the ratio to the perimeter of the photosensitive surface is as large as possible.

For convenience of description, the photosensitive surface is divided into two parts, ie, an edge part and a non-edge part (or inner part). Usually, the jitter mainly affects the outgoing light collected by the edge part, and the non-edge part is less affected, that is, the non-edge part can collect the outgoing light relatively stably. From another perspective, in the presence of jitter, since the intensity distribution of the outgoing light in the measurement area will change slightly, the light intensity value of the outgoing light received by the edge portion will change with the intensity distribution of the outgoing light. However, a large change occurs, and since most of the outgoing light located in the non-edge portion can be collected by the photosensitive surface relatively stably, the light intensity value of the outgoing light received by the non-edge portion can remain relatively stable. Therefore, in order to effectively suppress the adverse effect of jitter on the measurement results, the ratio of the area corresponding to the non-edge portion to the area of the photosensitive surface can be made as large as possible, and the larger the ratio, the better the effect of weakening the adverse effect. The edge portion can be represented by the perimeter of the photosensitive surface, and the non-edge portion can be represented by the area of the photosensitive surface. Thereby, the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface can be made as large as possible.

Exemplarily, if the photosensitive surface 1 is a circular photosensitive surface, and the photosensitive surface 2 is a square photosensitive surface, in the case of the same perimeter, since the area of the photosensitive surface 1 is larger than the area of the photosensitive surface 2, the area of the photosensitive surface 1 is The ratio to the perimeter is greater than the ratio of the area of the photosensitive surface 2 to the perimeter. Therefore, the photosensitive surface 1 has a better effect of reducing adverse effects than the photosensitive surface 2 has.

It should be noted that when the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold, the condition that the area of the photosensitive surface is greater than or equal to the area threshold is satisfied. For most shapes of photosensitive surfaces, if the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold, the size of the photosensitive surface is actually limited. This is because for most shapes of graphics, the ratio of the area to the perimeter of the graphic has a positive correlation with the size of the area, that is, the larger the ratio of the area to the perimeter of the graphic, the larger the area of the graphic.

Exemplarily, such as a circle, the area of the circle is πR ² , and the ratio of the area to the perimeter of the circle is R/2, where R represents the radius. Since the ratio of the area to the circumference of a circle is only related to the radius, and the size of the area of the circle is only related to the radius, therefore, the ratio of the area to the circumference of a circle has a positive correlation with the size of the area. The ratio of the area of the circle to the perimeter also defines the size of the area of the circle. Another example is a square, the area of the square is a ² , the ratio of the area to the perimeter of the square is a/4, and a represents the length of the side. Since the ratio of the area to the perimeter of a square is only related to the length of the side, and the size of the area of the square is only related to the length of the side, therefore, the ratio of the area to the perimeter of the square has a positive correlation with the size of the area, if the square is defined The ratio of the area to the perimeter also defines the size of the area of the square.

According to an embodiment of the present disclosure, the ratio threshold is greater than or equal to 0.04 mm.

According to the embodiments of the present disclosure, the area of the photosensitive surface of the present disclosure is a relatively large area, that is, the area of the photosensitive surface is a large area within an area range. This case will be described below.

First, the area of the photosensitive surface cannot be too small. Since the large-area photosensitive surface in the embodiment of the present disclosure refers to the area of the photosensitive surface such that the photosensitive surface can collect the light intensity value of the outgoing light emitted from the outgoing position within the preset anti-shake range, the large-area photosensitive surface of the embodiment of the present disclosure is The large area of the area photosensitive surface is a large area used to achieve anti-shake. At the same time, because the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface can be used to characterize the area of the photosensitive surface, the photosensitive surface can capture the preset anti-shake surface. The light intensity value of the outgoing light emitted from the outgoing position within the jitter range, and under normal circumstances, the ratio of the area of the photosensitive surface to the perimeter has a positive correlation with the area of the photosensitive surface. Therefore, if the area of the photosensitive surface is If the ratio of the perimeter of the photosensitive surface is greater than or equal to the ratio threshold, the area of the photosensitive surface is actually limited, that is, the ratio of the area to the perimeter of the photosensitive surface is greater than or equal to the ratio threshold. The area cannot be too small.

Second, the area of the photosensitive surface should not be too large. The embodiment of the present disclosure requires that the ratio of the average optical path length of the outgoing light received by the photosensitive surface to the total optical path in the target tissue layer is greater than or equal to the proportional threshold, and/or the area of the photosensitive surface is determined according to the characteristics of the tissue structure. The above description of the photosensitive surface area should not be too large.

From this, it can be explained that the area of the photosensitive surface of the embodiment of the present disclosure is a relatively large area, that is, a large area within an area range.

In addition, although the area of the photosensitive surface is large, the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is not large due to the large perimeter of the photosensitive surface. The ratio of the perimeters of the surfaces is smaller than the ratio threshold. Therefore, it may be difficult for an absolutely large-area photosensitive surface to meet the requirements of anti-shake. There may also be cases where the area of the photosensitive surface is too small and the perimeter of the photosensitive surface is large, so that the ratio of the area of the photosensitive surface to the perimeter of the photosensitive surface is less than the ratio threshold. Therefore, the area of the photosensitive surface is too small. jitter requirements.

According to an embodiment of the present disclosure, the photosensitive surface is in contact or non-contact with the surface of the measurement area.

According to embodiments of the present disclosure, the form of tissue composition measurement may include contact measurement and non-contact measurement. Among them, the contact measurement can prevent the interference light from being received by the photosensitive surface, thereby improving the reliability of the measurement results. Non-contact measurement can avoid the influence of interfering factors such as temperature and pressure on the measurement results, thereby improving the reliability of the measurement results.

If the photosensitive surface is set in contact with the surface of the measurement area, the form of tissue composition measurement can be considered as contact measurement. If the photosensitive surface is set to be non-contact with the surface of the measurement area, the form of tissue composition measurement can be considered as non-contact measurement.

According to an embodiment of the present disclosure, the distance of the photosensitive surface from the surface of the measurement area is less than or equal to the first distance threshold and the efficiency of the photosensitive surface receiving the outgoing light is greater than or equal to the efficiency threshold.

According to the embodiments of the present disclosure, since the photosensitive surface is made of photosensitive material, the area of the photosensitive surface is continuous, therefore, the reception of a wide range of light intensity values can be realized, and the efficiency of receiving outgoing light can be improved. Based on this, even in the case of being close to the surface of the measurement area, that is, when the distance between the photosensitive surface and the surface of the measurement area is less than or equal to the first distance threshold, the efficiency of receiving outgoing light greater than or equal to the efficiency threshold can be achieved.

According to an embodiment of the present disclosure, before irradiating the measurement area with the incident light of a single preset wavelength, the method may further include the following operations.

Identify work features. From the positioning features, a measurement area is determined, wherein the measurement area is an area that satisfies the reproducibility of the controllable measurement conditions. The measurement probe is arranged at a position corresponding to the measurement area, wherein the measurement probe includes M photosensitive surfaces.

According to the embodiments of the present disclosure, during the measurement of living tissue components, changes in the measurement conditions may overwhelm the weak measured tissue component signals, making it difficult to obtain the real measured tissue component signals, and have a greater impact on the measurement results .

The inventors found that since the mechanism of the variation of the controllable measurement conditions affecting the measurement result is different, it is difficult to suppress its influence on the measurement result by adopting a mathematical algorithm. However, it is found that the controllable measurement conditions can achieve reproducibility through effective control, so that its influence on the measurement results can be reduced to a negligible level, that is, the influence of the changes of the controllable measurement conditions on the measurement results and the influence of random noise on the measurement results. The level of impact is comparable. Therefore, for the controllable measurement conditions, the inventor proposes that the most suitable processing method is to use an effective control method to control the controllable measurement conditions to achieve its reproducibility. Among them, the effective control method is not a mathematical algorithm, which can be implemented with hardware design. The reproducibility of the controllable measurement conditions may refer to maintaining the controllable measurement conditions within a preset variation range during each tissue composition measurement, so that the controllable measurement conditions remain unchanged or substantially unchanged.

According to the embodiments of the present disclosure, the use of an effective control method to control the controllable measurement conditions can reduce the influence of changes in the controllable measurement conditions on the measurement results to a negligible level, thereby avoiding complex mathematical algorithms for processing , thereby improving the reliability of the measurement results, in addition to reducing the difficulty of data processing and reducing the amount of data processing.

The following describes the use of an effective control method to achieve the reproducibility of the controllable measurement conditions, so as to reduce the influence of the variation of the controllable measurement conditions on the measurement results to a negligible level. In the embodiments of the present disclosure, the measurement posture reproducibility and the measurement area reproducibility are mainly aimed at. The measurement posture refers to the posture of the limb supporting the measurement site. And in the related art, no relevant content for measuring posture is found.

One is to measure the regional reproducibility. The positioning deviation of the measurement area is caused by the non-uniformity of tissue distribution and the difference in the flat state of the skin surface. When the relative position between the measurement probe and the measurement area is deviated, the transmission path of light in the tissue will be changed. It can be seen that in order to achieve the reproducibility of the controllable measurement conditions, it is necessary to ensure the reproducibility of the measurement area as much as possible.

Second, measure postural reproducibility. In the measurement of tissue components, it is difficult for the measured object to keep the same measurement posture, and the change of the measurement posture will lead to changes in the state of the skin in the measurement area, which in turn leads to changes in the transmission path of light in the tissue. Therefore, the measurement posture changes. Positioning errors will occur and affect the reliability of the measurement results. The skin state may include the shape of the skin surface and the internal structure of the skin. It can be seen that it is necessary to achieve the reproducibility of the measurement posture. The purpose of the measurement posture positioning is to make the measurement posture when the tissue component measurement is performed as the target measurement posture, that is, when the tissue component measurement is performed, if the current measurement posture is not the target measurement posture, then the current measurement posture needs to be adjusted to the target measurement posture, The target measurement posture is a measurement posture that satisfies the reproducibility of the controllable measurement conditions.

But in fact, the importance of achieving the reproducibility of measured poses is often overlooked, which is reflected in the following two aspects.

First, the reproducibility of the measurement pose was not found to be an important factor affecting the reliability of the measurement results. In the related art, it is generally believed that in terms of controllable measurement conditions, the most important reason for affecting the reproducibility of controllable measurement conditions is the reproducibility of the measurement area. Improve the reliability of measurement results without considering other reasons. In other words, in the related art, the improvement direction revolves around how to improve the positioning accuracy of the measurement area, and it is not found that in terms of controllable measurement conditions, measurement posture reproducibility is also an important factor affecting the reliability of measurement results.

In addition, according to the above analysis, even if the reproducibility of the measurement area is achieved, when the posture of the limb supporting the measurement site changes, the internal structure of the skin at the measurement area will also change, resulting in the transmission path of light in the tissue. Variations, therefore, also affect the reliability of the measurement results. In other words, only ensuring the reproducibility of the measurement area and ignoring the reproducibility of the measurement posture is not conducive to improving the reliability of the measurement results.

Second, there is no effective way to achieve measurement posture reproducibility. Since the factors affecting the reliability of the measurement results have not been deeply studied, and the importance of achieving the reproducibility of the measurement posture has not been recognized, it is considered that in the measurement of tissue components, it is sufficient to use a method in which the subject itself maintains a stable body. Realize the control of the measurement posture, that is, if the measured object thinks that its body state has not changed, the measurement posture is well controlled. However, in most cases, the change of the measurement posture cannot be perceived by the measured object. Therefore, the error of this method of realizing the reproducibility of the measurement posture is large, which will greatly interfere with the reliability of the measurement result. That is, even if a method is adopted to control the measurement posture, since the importance of realizing the reproducibility of the measurement posture is not recognized, this method cannot substantially guarantee the reproducibility of the measurement posture.

It can be seen that in order to achieve the reproducibility of the measurement area, it is necessary to ensure the reproducibility of the measurement posture as much as possible, that is, to achieve accurate positioning of the measurement posture. Based on the above, the reproducibility of the measurement area needs to be premised on the reproducibility of the measurement posture, and therefore, the positioning of the measurement area needs to be premised on the positioning of the measurement posture.

During the positioning process, the positioning can be carried out according to the positioning features. The positioning feature may include a posture positioning feature and an area positioning feature, the posture positioning feature is used for positioning the measurement posture, and the area positioning feature is used for positioning the measurement area. The posture positioning feature can be set on the measured object or the non-measured object, the regional positioning feature can be set on the measured object or the non-measured object, and the non-measured object can include a measuring probe or other devices. The positioning features may include artificially set positioning features or inherent features on the measured object, wherein the inherent features may include palm prints, fingerprints, birthmarks, moles or scabs and the like.

According to the embodiment of the present disclosure, if the positioning feature is set manually, since the positioning feature set manually usually fades gradually over time, it needs to be set again, which may introduce new errors and affects the positioning accuracy. The inherent feature has better stability, and it is not easy to generate setting errors.

In order to reduce the complexity of the positioning and improve the positioning accuracy, a setting method in which the inherent features on the measured object are used as the positioning features can be adopted. However, even if the inherent feature on the measured object is used as the setting method of the posture positioning feature, the internal structure of the skin will be affected by the change of the measurement posture, which will also cause the positioning deviation of the measurement area. The position on the object is not arbitrary, and needs to be determined according to the measurement site and the bone-muscle relationship between the measurement site and the surrounding site. Exemplarily, for example, the measurement site is the extensor side of the forearm, and its peripheral site includes the wrist. For the forearm extension side, since the change of the wrist state will greatly affect the skin condition of the forearm extension side, in order to improve the positioning accuracy, positioning features can be set on the forearm extension side and the back of the hand respectively. It should be noted that, if there is no inherent feature that can be used as the positioning feature, the positioning feature can be set manually. Exemplarily, for example, the positioning feature may be a dot-shaped mark point or a graphic mark point, and the graphic mark point may include a cross mark point.

According to an embodiment of the present disclosure, the positioning features include a first gesture positioning feature and an area positioning feature. Determining the measurement area according to the positioning feature may include the following operations.

According to the first posture positioning feature, the current measurement posture of the measured object is adjusted to a target measurement posture, wherein the target measurement posture is a measurement posture that satisfies the reproducibility of the controllable measurement condition. When the current measurement posture is the target measurement posture, the measurement area is determined according to the area positioning feature.

According to the embodiments of the present disclosure, when positioning the measurement posture and the measurement area, the premise of realizing the positioning of the measurement area is to realize the positioning of the measurement posture, and in the subsequent measurement process after the positioning of the measurement area is completed, usually the measurement area does not need to be positioned again. , there may also be situations where measurement pose positioning is required. The condition for completing the positioning of the measurement posture is that the current measurement posture is the target measurement posture, and the target measurement posture is the measurement posture that satisfies the reproducibility of the controllable measurement conditions.

According to the embodiment of the present disclosure, the reason why the above-mentioned situation that measurement posture positioning is required is that, in the embodiment of the present disclosure, in order to bring a better user experience to the measured object, a non-measurement method can be used. When measuring, the measurement position is allowed to move within a certain range, and the measurement posture is positioned during measurement. When measuring, it is necessary to ensure that the current measurement posture is the target measurement posture. Therefore, if the current measurement posture is not the target measurement posture, it is necessary to Adjust the measurement posture to ensure that the current measurement posture is the target measurement posture.

Based on the above, the positioning can be divided into the positioning of the first measurement posture, the positioning of the measurement area, and the positioning of the second measurement posture. Wherein, the positioning of the first measurement posture can be understood as the measurement posture positioning of the measurement area in cooperation. The re-measurement posture positioning can be understood as the measurement posture positioning performed when the measurement probe is set after the position corresponding to the measurement area and the measurement posture is not the target measurement posture.

According to an embodiment of the present disclosure, the area location feature is used to perform measurement area location. The posture localization feature adopted for the first measurement of posture localization is referred to as the first posture localization feature. The posture location feature used to measure the posture location again is referred to as the second posture location feature. Both the first posture positioning feature and the second posture positioning feature are used to perform measurement posture positioning, and the area positioning feature, the first posture positioning feature and the second posture positioning feature may all be the same, partially the same or all different. The number of area location features, first gesture location features, and second gesture location features may include one or more.

During the first measurement posture positioning and measurement area positioning, the current measurement posture of the measured object can be adjusted according to the first posture positioning feature so that the first posture positioning feature matches the preset feature, and the first posture positioning feature matches the preset feature. In the case of feature matching, it can be determined that the current measurement posture is the target measurement posture. When the current measurement posture is the target measurement posture, the measurement area is determined according to the area positioning feature. Thus, the positioning of the measurement posture and the measurement area is completed.

It should be noted that, determining the measurement area according to the regional positioning feature may be understood as determining the area corresponding to the regional positioning feature as the measurement area, which includes determining the area where the regional positioning feature is located as the measurement area. Or another area having an associated relationship with the area positioning feature is determined as the measurement area.

By locating the feature according to the first posture and the region locating feature, the positioning of the measurement area and the positioning of the measurement posture are realized synchronously.

According to an embodiment of the present disclosure, disposing the measurement probe at a position corresponding to the measurement area may include the following operations.

The measuring probe is arranged at a position corresponding to the measurement area by the fixing part, wherein the fixing part and the measuring probe are integrated, partially separated or completely separated.

According to an embodiment of the present disclosure, the fixing part is used to fix the measuring probe, and the fixing part and the measuring probe may be integrated, partially or completely independent, that is, the fixing part may be used as a component of the measuring probe, and may be mutually connected with the measuring probe. The two independent parts can also be part of the measuring probe, and the other part and the measuring probe are independent parts. The fixing part may include a fixing seat and a first fitting, or the fixing part may comprise a second fitting. The first matching piece is used for setting the fixing base at a position corresponding to the measurement area, and the fixing base is used for setting the measuring probe. The second fitting is used to set the measurement probe at a position corresponding to the measurement area.

If the fixing part includes a fixing base and a first fitting, the fixing base and the measuring probe are separate, and the first fitting and the fixing base are integrated or separate. If the fixing part includes the second fitting, the second fitting and the measuring probe are integral or separate.

According to an embodiment of the present disclosure, the fixing part includes a fixing seat and a first fitting part.

Setting the measurement probe at a position corresponding to the measurement area by the fixing portion may include the following operations.

The fixing base is arranged at a position corresponding to the measurement area through the first matching piece. Set the measuring probe to the holder.

According to an embodiment of the present disclosure, the measurement probe is not directly disposed at the position corresponding to the measurement area, but is disposed at the position corresponding to the measurement area through the fixing seat.

In the process of tissue composition measurement, if the measurement probe is set at the position corresponding to the measurement area through the fixing seat, since the fixing seat can be set in the measurement area for a long time without departing from the measurement area, the measurement probe can be set during measurement. It is attached to the fixed seat, and it is separated from the fixed seat during non-measurement. In addition, since the fixing base is arranged at a position corresponding to the measurement area, when the measuring probe is separated from the fixing base and then installed on the fixing base, a good positioning accuracy can still be maintained, and the positioning difficulty of the measuring probe is reduced.

According to an embodiment of the present disclosure, the skin state of the skin at the measurement area satisfies the first preset condition during the process of setting the fixing seat at the position corresponding to the measurement area by the first fitting.

According to an embodiment of the present disclosure, the skin state of the skin at the measurement area satisfies the second preset condition during the process of disposing the measurement probe on the fixing seat.

According to the embodiments of the present disclosure, since the action of fixing the fixing seat will affect the skin condition of the skin at the corresponding position, thereby affecting the positioning accuracy of the measurement area, in order to ensure the positioning accuracy of the measurement area, the first fitting During the process of fixing the fixing base, it is ensured that the skin state of the skin at the measurement area satisfies the first preset condition. Wherein, the first preset condition may refer to the change of the skin state of the skin at the corresponding position during the process of fixing the fixing seat by the first fitting member within the first preset range. Changes in skin condition can include skin deformation. Correspondingly, the first preset range may include the first preset deformation range.

According to the embodiment of the present disclosure, since the action of fixing the measurement probe will affect the skin condition of the skin at the corresponding position, thereby affecting the positioning accuracy of the measurement area, in order to improve the positioning accuracy of the measurement area, the fixing seat can be fixed During the process of measuring the probe, it is ensured that the skin state of the skin in the measurement area satisfies the second preset condition. Wherein, the second preset condition may refer to the change of the skin state of the skin at the corresponding position during the process of fixing the measurement probe on the fixing base within the second preset range. Changes in skin condition can include skin deformation. Correspondingly, the second preset range may include a second preset deformation range.

According to an embodiment of the present disclosure, the measurement probe does not move in the holder.

According to the embodiments of the present disclosure, when the measurement probe is fixed on the fixing base, the problem of affecting the reproducibility of the controllable measurement conditions also occurs due to the weak fixing. In order to solve this problem, it can be ensured as far as possible that the measurement probe does not move in the fixed seat during the tissue composition measurement process.

According to an embodiment of the present disclosure, the fixing part includes a second fitting.

The measurement probe is set at a position corresponding to the measurement area through the second fitting.

According to the embodiments of the present disclosure, for the manner in which the measurement probe is arranged at the position corresponding to the measurement area, in addition to the above-mentioned method of arranging the measurement probe at the position corresponding to the measurement area through the fixing seat, a direct The method of disposing the measuring probe at the position corresponding to the measuring area does not require a fixing seat, but requires the cooperation of the second fitting.

It should be noted that the above-mentioned need of no fixing seat may include the following two understandings. First, the measuring probe is provided with a structure integral with it, which plays the same role as the independent fixing seat. Second, the measuring probe is not provided with a structure that plays the same role as the independent fixing seat.

According to an embodiment of the present disclosure, the skin state of the skin at the measurement area satisfies the third preset condition during the process of setting the measurement probe at the position corresponding to the measurement area through the second fitting.

According to the embodiment of the present disclosure, since the action of fixing the measurement probe will affect the skin state of the skin at the corresponding position, thereby affecting the positioning accuracy of the measurement area, in order to ensure the positioning accuracy of the measurement area, the second fitting can be made During the process of fixing the measurement probe, it is ensured that the skin state of the skin at the measurement area satisfies the third preset condition. Wherein, the third preset condition may refer to the change of the skin state of the skin at the corresponding position during the process of fixing the measurement probe by the second fitting member within the third preset range. Changes in skin condition can include skin deformation. Correspondingly, the third preset range may include a third preset deformation range.

According to an embodiment of the present disclosure, determining the measurement area according to the area positioning feature may include the following operations.

Get the first projected feature. In the case where it is determined that the regional positioning feature does not match the first projected feature, the position of the measuring probe and/or the fixing portion is adjusted until the regional positioning feature matches the first projected feature. When it is determined that the region positioning feature matches the first projection feature, the region corresponding to the measurement probe and/or the fixing portion is determined as the measurement region.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the positioning of the measurement area, an optical method can be used, that is, the area positioning feature is matched with the first projection feature, and the measurement area is determined according to the matching result, wherein the first The projection feature is formed according to an optical method, that is, a light spot of a preset shape is projected by the light source, and the shape of the light spot can be determined according to the regional positioning feature. Exemplarily, the light spot with the preset shape is a cross light spot.

According to an embodiment of the present disclosure, after obtaining the first projected feature by using the structure for projecting the first projected feature, it is determined whether the regional positioning feature matches the first projected feature, and if it is determined that the regional positioning feature does not match the first projected feature Next, the position of the measuring probe and/or the fixing base can be adjusted so that the regional positioning feature matches the first projection feature until the regional positioning feature matches the first projection feature. In the case where it is determined that the region positioning feature matches the first projection feature, it can be indicated that the region where the measurement probe and/or the fixing base are currently located is the measurement region.

According to an embodiment of the present disclosure, the structure for projecting the first projection feature may be provided on the object to be measured, the measurement probe, the holder, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The area locating feature may be provided on at least one of the measurement probe, the mount, the object to be measured, and other objects. The adjustment process based on the optical method will be described below from two perspectives, the setting position of the structure for projecting the first projection feature and the setting position of the regional positioning feature.

Described from the perspective of the setting position of the structure for projecting the first projected feature.

First, if the structure for projecting the first projection feature is arranged on the object to be measured, the area positioning feature can be arranged on at least one of the object to be measured, the measuring probe, the fixed seat and other objects. It should be noted that, if the regional positioning feature is set on the object to be measured or other objects, the positioning of the measurement region can be achieved by the following methods, that is, according to the regional positioning feature and the first projection feature, the position of the measuring probe and/or the fixed seat is adjusted. , until the regional positioning feature matches the first projection feature. The matching of the regional positioning feature and the first projection feature here means that the regional positioning feature is blocked by the measuring probe and/or the fixed seat, so that the first projection feature cannot be projected to the region. The location of the work feature. If the region positioning feature does not match the first gesture positioning feature, there is at least one first projection feature that can be projected to the location where the region positioning feature is located.

Second, if the structure for projecting the first projection feature is provided on the measuring probe, the regional positioning feature cannot be set on the measuring probe, but can be set on the object to be measured, the holder or other objects. It should be noted that, if the area positioning feature is set on the fixed seat, and the positioning of the measuring probe is realized by setting the measuring probe at the position corresponding to the measuring area through the fixing part provided with the fixed seat, then in order to be able to realize the positioning of the measuring probe. The positioning of the measurement area can be achieved by adjusting the position of the fixed seat. Before the matching of the regional positioning feature and the first projection feature is achieved, the position of the measuring probe is fixed. According to the regional positioning feature and the first projection feature, the position of the fixing seat is adjusted until the regional positioning feature matches the first projection feature. , in the case of matching the two, the area corresponding to the fixed seat is determined as the measurement area, so that the measurement probe can be set on the fixed seat.

Thirdly, if the structure for projecting the first projection feature is set on the fixed seat, the regional positioning feature cannot be set on the fixed base, but can be set on the object to be measured, the measuring probe or other objects. It should be noted that, if the area positioning feature is provided on the measurement probe, and the measurement probe is positioned by setting the measurement probe at the position corresponding to the measurement area through the fixing part provided with the fixing seat, then in order to be able to realize the positioning of the measurement probe. The positioning of the measurement area can be achieved by adjusting the position of the fixed seat. Before the matching of the regional positioning feature and the first projection feature is achieved, the position of the measuring probe is fixed. According to the regional positioning feature and the first projection feature, the position of the fixing seat is adjusted until the regional positioning feature matches the first projection feature. , in the case of matching the two, the area corresponding to the fixed seat is determined as the measurement area, so that the measurement probe can be set on the fixed seat.

Fourth, if the structure for projecting the first projection feature is set on other objects, the area positioning feature can be set on at least one of the measured object, the measuring probe, the fixed seat and other objects. It should be noted that, if the regional positioning feature is set on the measured object or other objects, the structure used to project the first projection feature can be set on the measured object, and the regional positioning feature is set on the measured object or other objects. The positioning of the measurement area is implemented in a similar manner, which will not be repeated here.

From the perspective of the setting position of the regional positioning feature.

First, if the area positioning feature is set on the object to be measured, the structure for projecting the first projection feature can be set on the object to be measured, a measuring probe, a fixed seat or other objects. It should be noted that, if the structure for projecting the first projection feature is set on the object to be measured or other objects, the positioning of the measurement area can be achieved by the following methods, that is, according to the area positioning feature and the first projection feature, adjust the measurement probe and / or the position of the fixed seat, until the regional positioning feature matches the first projection feature, and the matching of the regional positioning feature with the first projected feature here means that the regional positioning feature is blocked by the measuring probe and/or the fixed seat, so that the first The projected feature cannot be projected to the location where the area work feature is located. If the region positioning feature does not match the first gesture positioning feature, there is at least one first projection feature that can be projected to the location where the region positioning feature is located.

Second, if the area positioning feature is set on the measuring probe, the structure for projecting the first projection feature is separate from the measuring probe, and can be set on the object to be measured, the holder or other objects. It should be noted that, if the structure for projecting the first projection feature is disposed on the fixed seat, the description in the corresponding part above can be referred to, and details are not repeated here.

Thirdly, if the area locating feature is set on the fixing base, the structure for projecting the first projection feature is separate from the fixing base, and can be set on the object to be measured, the measuring probe or other objects. It should be noted that, if the structure for projecting the first projection feature is disposed on the measurement probe, reference may be made to the description in the corresponding part above, which will not be repeated here.

Fourth, if the regional positioning feature is set on other objects, the structure for projecting the first projection feature can be set on the object to be measured, the measuring probe, the fixed seat or other objects. It should be noted that, if the structure for projecting the first projection feature is provided on the object to be measured or other objects, reference may be made to the description in the corresponding part above, and details are not repeated here.

Exemplarily, FIG. 5 schematically shows a schematic diagram of realizing the positioning of the measurement area based on an optical method according to an embodiment of the present disclosure. The area locating feature in Figure 5 is provided on the measuring probe. FIG. 6 schematically shows a schematic diagram of another implementation of positioning the measurement area based on an optical method according to an embodiment of the present disclosure. In Figure 6, the regional positioning feature is set on the measured object.

The positioning of the measurement area is realized by the optical method. On the one hand, since the position and angle of the light source can be flexibly adjusted, it can be easily matched with the regional positioning feature. Therefore, the regional positioning feature can be set flexibly, thereby reducing the setting of the regional positioning feature. difficulty. On the other hand, by adjusting the shape of the outgoing light spot, the matching with the regional positioning features can be better achieved, and the positioning accuracy can be improved.

Acquire the first target image. A first template image is acquired, wherein the first template image includes regional positioning features. If it is determined that the first target image does not match the first template image, adjust the position of the measuring probe and/or the fixing part to acquire a new first target image until the new first target image matches the first template image . When it is determined that the first target image matches the first template image, an area corresponding to the measurement probe and/or the fixing portion is determined as a measurement area.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the positioning of the measurement area, an image matching method can be used, that is, the first target image is matched with the first template image, and the measurement area is determined according to the matching result. Wherein, the first template image may include a region positioning feature, and the position of the region positioning feature in the first template image is a preset position. In the process of matching the first target image with the first template image, the first target image may be a target image that does not include regional positioning features, or may include regional positioning features but the position of the regional positioning features in the first target image is not The target image at the preset position may also be a target image including a region positioning feature and the position of the region positioning feature in the first target image is a preset position. Since the first template image includes the region positioning feature at the preset position, if the first target image matches the first template image, it can be said that the first target image includes the region positioning feature and the region positioning feature is in the first target image is the default position. In other words, the purpose of matching the first target image with the first template image is to make the acquired first target image include regional positioning features and the positions of the regional positioning features in the first target image are preset positions.

According to the embodiment of the present disclosure, when it is determined that the first target image matches the first template image, it can be stated that the area where the measurement probe and/or the fixing base are currently located is the measurement area. Wherein, determining whether the first target image matches the first template image may include determining the similarity between the first target image and the first template image. When the similarity is greater than or equal to the similarity threshold, it is determined that the first target image matches the first template image. In the case that the similarity is less than the similarity threshold, it is determined that the first target image does not match the first template image. Determining the similarity between the first target image and the first template image may include performing a correlation analysis on the first target image and the first template image to obtain a correlation coefficient, and determining the similarity between the first target image and the first template image according to the correlation coefficient.

According to an embodiment of the present disclosure, the structure for acquiring the first target image may be disposed on the object to be measured, the measurement probe, the fixed seat, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The area locating feature may be provided on at least one of the measurement probe, the mount, the object to be measured, and other objects. For the description of the structure and the region positioning feature used for acquiring the first target image, reference may be made to the description of the structure and region positioning feature used for projecting the first projection feature, and details are not repeated here. The difference is that if the structure for acquiring the first target image is provided on the measuring probe, the area positioning feature may be provided on at least one of the object to be measured, the measuring probe, the holder and other objects. If the structure for capturing the first target image is provided on the mount, the area positioning feature may be provided on at least one of the object to be measured, the measurement probe, the mount, and other objects.

Exemplarily, FIG. 7 schematically shows a schematic diagram of positioning a measurement area based on an image matching method according to an embodiment of the present disclosure. The area locating feature in Figure 7 is provided on the measuring probe. FIG. 8 schematically shows a schematic diagram of implementing positioning of a measurement area based on another image matching method according to an embodiment of the present disclosure. In Fig. 8, the regional positioning feature is set on the measured object.

A second target image is acquired, wherein the second target image includes regional localization features. In the case where it is determined that the position of the regional positioning feature in the second target image is not the first preset position, adjust the position of the measuring probe and/or the fixing part to acquire a new second target image until the new second target image The position of the positioning feature in the middle area is the first preset position. When it is determined that the position of the area positioning feature in the new second target image is the first preset position, the area corresponding to the measurement probe and/or the fixing part is determined as the measurement area.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement area positioning, an imaging method can be used to achieve, that is, if the position of the area positioning feature in the second target image is the first preset position, it can be indicated that the completion of location of the measurement area.

According to the embodiment of the present disclosure, the process of using the imaging method to realize the measurement area positioning is the process of determining whether the position of the area positioning feature in the second target image is the first preset position. If the area positioning feature is in the second target image is not the first preset position, the position of the measuring probe and/or the fixing seat can be adjusted to obtain a new second target image, until the position of the regional positioning feature in the new second target image is the first preset position set location. In the case where the position of the area positioning feature in the new second target image is the first preset position, it can be stated that the area where the measurement probe and/or the fixing base are currently located is the measurement area.

According to an embodiment of the present disclosure, the structure for acquiring the second target image may be provided on the object to be measured, the measurement probe, the fixed seat or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The area locating feature may be provided on at least one of the measurement probe, the mount, the object to be measured, and other objects. For the description of the structure and the region positioning feature used for acquiring the second target image, reference may be made to the description of the structure and region positioning feature used for projecting the first projection feature, which will not be repeated here.

Exemplarily, FIG. 9 schematically shows a schematic diagram of positioning the measurement area implemented by an imaging method according to an embodiment of the present disclosure. The area locating feature in Figure 9 is provided on the measurement probe. FIG. 10 schematically shows a schematic diagram of implementing positioning of a measurement area based on another imaging method according to an embodiment of the present disclosure. In Figure 10, the regional positioning feature is set on the measured object. The movement of the measuring probe and the fixing base in FIG. 10 changes the relative positions of the two and the regional positioning feature, so that the position of the regional positioning feature presented in the image is located at the first preset position.

According to an embodiment of the present disclosure, adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature may include the following operations.

Get the second projected feature. In the case where it is determined that the first posture locating feature does not match the second projection feature, the current measurement posture is adjusted until the first posture locating feature and the second projection feature match. When it is determined that the first posture positioning feature matches the second projection feature, it is determined that the current measurement posture is the target measurement posture.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement posture positioning, an optical method can be used to achieve, that is, the first posture positioning feature and the second projection feature are matched, and the target measurement posture is determined according to the matching result, wherein , the second projection feature is formed according to an optical method, that is, the second projection feature is formed by projecting a light spot of a preset shape by the light source, and the shape of the light spot can be determined according to the first posture positioning feature. That is, for the measured object, a second projection feature matching the first posture positioning feature is set according to the first posture positioning feature, so that the current measurement posture matching the first posture positioning feature and the second projection feature is the target measurement posture.

According to an embodiment of the present disclosure, the structure for projecting the second projection feature may be provided on the object to be measured, the measurement probe, the mount, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The first posture locating feature may be provided on at least one of the measuring probe, the holder, the measured object and other objects. The adjustment process based on the optical method will be described below from two angles of the setting position of the structure for projecting the second projection feature and the setting position of the first posture positioning feature.

Described from the perspective of the setting position of the structure for projecting the second projection feature.

First, if the structure for projecting the second projection feature is arranged on the measured object, the first posture positioning feature can be arranged on at least one of the measured object, the measuring probe, the fixed seat and other objects. It should be noted that, if the first posture positioning feature is provided on the measurement probe, in order to realize the positioning of the measurement posture, the position of the measurement probe needs to be fixed during the first measurement posture positioning stage. Similarly, if the first posture positioning feature is provided on the fixed seat, in order to realize the positioning of the measurement posture, it is necessary to make the position of the fixed seat be fixed during the first measurement posture positioning stage.

Second, if the structure for projecting the second projection feature is arranged on the measuring probe, the first posture positioning feature cannot be arranged on the measuring probe, but can be arranged on the object to be measured, the holder or other objects. It should be noted that the position of the measurement probe needs to be fixed in the first measurement posture positioning stage. In addition, if the first posture positioning feature is set on the fixed seat, the positioning of the first measurement posture can be realized by the following method, that is, according to the first posture positioning feature and the second projection feature, the current measurement posture of the measured object is adjusted until the first posture positioning feature and the second projection feature are adjusted. The posture positioning feature matches the second projection feature. The matching of the first posture positioning feature and the second projection feature here means that the first posture positioning feature is blocked by the measured object, so that the second projection feature cannot be projected to the first posture. The location of the work feature. If the first gesture location feature does not match the second gesture location feature, then there is at least one second projection feature that can be projected to the location where the first gesture location feature is located. If the first posture positioning feature is set on other objects, the positioning of the measurement posture can be implemented in a manner similar to that when the first posture positioning feature is set on the fixed seat, which will not be repeated here.

Third, if the structure for projecting the second projection feature is installed on the fixed seat, the first posture positioning feature cannot be installed on the fixed seat, but can be installed on the object to be measured, the measuring probe or other objects. It should be noted that, it is necessary to make the position of the fixed seat be fixed in the first measurement posture positioning stage. In addition, if the first posture positioning feature is provided on the measuring probe or other object, it can be used in a similar manner as the structure for projecting the second projection feature is provided on the measuring probe, and the first posture positioning feature is provided on the holder or other object The positioning of the measurement posture is realized, which is not repeated here.

Fourth, if the structure for projecting the second projection feature is set on other objects, the first posture positioning feature can be set on at least one of the measured object, the measuring probe, the fixed seat and other objects. It should be noted that, if the first posture positioning feature is set on the measuring probe, the fixed seat or other objects, the same structure as the structure used to project the second projection feature can be set on the measuring probe, and the first posture positioning feature is set on the fixed position. The positioning of the measurement posture can be achieved in a similar manner to a seat or other objects, which will not be repeated here.

From the perspective of the setting position of the first posture positioning feature.

First, if the first posture positioning feature is set on the measured object, the structure for projecting the second projection feature can be set on the measured object, a measuring probe, a fixed seat or other objects. It should be noted that, if the structure for projecting the second projection feature is provided on the measurement probe, it is required that the position of the measurement probe is fixed in the first measurement posture positioning stage. Similarly, if the structure for projecting the second projection feature is arranged on the fixed seat, it is necessary to make the position of the fixed seat be fixed during the first measurement of the posture positioning stage.

Second, if the first posture positioning feature is set on the measuring probe, the structure for projecting the second projection feature is separate from the measuring probe, and can be set on the object to be measured, the holder or other objects. It should be noted that, if the structure for projecting the second projection feature is disposed on the object to be measured, the holder or other objects, the description in the corresponding part above can be referred to, and details are not repeated here.

Thirdly, if the first posture locating feature is set on the fixed base, the structure for projecting the second projection feature is separate from the fixed base, and can be set on the object to be measured, the measuring probe or other objects. It should be noted that, if the structure for projecting the second projection feature is provided on the object to be measured, the measuring probe or other objects, reference may be made to the description of the corresponding part above, and details are not repeated here.

Fourth, if the first posture positioning feature is set on other objects, the structure for projecting the second projection feature can be set on the measured object, the measuring probe, the fixed seat or other objects. It should be noted that, if the structure for projecting the second projection feature is provided on the object to be measured, the measuring probe, the fixed seat or other objects, the description of the corresponding part above can be referred to, and details are not repeated here.

Exemplarily, FIG. 11 schematically shows a schematic diagram of realizing the positioning of the measurement posture based on an optical method according to an embodiment of the present disclosure. In FIG. 11 , the first posture positioning feature is set on the measured object.

The positioning of the measurement posture is realized by an optical method. On the one hand, since the position and angle of the light source can be flexibly adjusted, it can be easily matched with the first posture positioning feature. Therefore, the first posture positioning feature can be flexibly set, thereby reducing the The difficulty of a pose localization feature setting. On the other hand, by adjusting the shape of the outgoing light spot, the matching with the first posture positioning feature can be better achieved, and the positioning accuracy can be ensured.

A third target image is acquired. A second template image is acquired, wherein the second template image includes the first gesture location feature. When it is determined that the third target image does not match the second template image, the current measurement posture is adjusted to obtain a new third target image until the new third target image matches the second template image. When it is determined that the new third target image matches the second template image, it is determined that the current measurement posture is the target measurement posture.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement posture positioning, an image matching method can be used, that is, the third target image is matched with the second template image, and the target measurement posture is determined according to the matching result. Wherein, the second template image may include a first posture locating feature and the position of the first posture locating feature in the second template image is a preset position. In the process of matching the third target image with the second template image, the third target image may be a target image that does not include the first posture positioning feature, or may include the first posture positioning feature but the first posture positioning feature is in the third The position of the target image is not the target image at the preset position, and may also be a target image including the first posture positioning feature and the position of the first posture positioning feature in the third target image is the preset position. Since the second template image includes the first posture localization feature at the preset position, if the third target image matches the second template image, it can be explained that the third target image includes the first posture localization feature and the first posture localization feature The position in the third target image is a preset position. In other words, the purpose of matching the third target image with the second template image is to make the acquired third target image include the first posture positioning feature and the position of the first posture positioning feature in the third target image is predetermined set location.

According to an embodiment of the present disclosure, the structure for acquiring the third target image may be provided on the object to be measured, the measurement probe, the fixed seat or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The first posture positioning feature may be provided on at least one of the measurement probe, the fixed seat, the object to be measured, and other objects. For the description of the structure for acquiring the third target image and the first posture positioning feature, reference may be made to the description of the structure for projecting the second projection feature and the first posture positioning feature, which will not be repeated here. The difference is that if the structure for acquiring the third target image is provided on the measuring probe, the first posture positioning feature may be provided on at least one of the measured object, the measuring probe, the fixing seat and other objects. If the structure for capturing the third target image is provided on the fixture, the first posture positioning feature may be provided on at least one of the object to be measured, the measurement probe, the fixture, and other objects.

Exemplarily, FIG. 12 schematically shows a schematic diagram of the positioning of the measurement posture implemented by an image matching method according to an embodiment of the present disclosure. In FIG. 12 , the first posture positioning feature is set on the measured object.

According to the embodiment of the present disclosure, in the case where it is determined that the third target image matches the second template image, it can be stated that the current measurement posture is the target measurement posture.

A fourth target image is acquired, wherein the fourth target image includes the first gesture positioning feature. In the case where it is determined that the position of the first posture positioning feature in the fourth target image is not at the second preset position, adjust the current measurement posture to obtain a new fourth target image until the first posture is positioned in the new fourth target image The location of the feature is at the second preset location. When it is determined that the position of the first posture positioning feature in the new fourth target image is at the second preset position, the current measurement posture is determined as the target measurement posture.

According to the embodiments of the present disclosure, in order to ensure the flexibility of use and the accuracy of measuring posture positioning, an imaging method can be used, that is, if the position of the first posture positioning feature in the fourth target image is the second preset position, it can be It indicates that the positioning of the measurement pose is completed.

According to the embodiment of the present disclosure, the process of using the imaging method to measure the posture positioning is the process of determining whether the position of the first posture positioning feature in the fourth target image is the second preset position. The position in the four target images is not the second preset position, then the current measurement posture can be adjusted to obtain a new fourth target image, until the position of the first posture positioning feature in the new fourth target image is the second preset position set location. When the position of the first posture positioning feature in the new fourth target image is the second preset position, it can be explained that the current measurement posture is the target measurement posture.

According to an embodiment of the present disclosure, the structure for acquiring the fourth target image may be disposed on the measured object, the measurement probe, the fixed seat or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The first posture positioning feature may be provided on at least one of the measurement probe, the fixed seat, the object to be measured, and other objects. For the description of the structure for acquiring the fourth target image and the first posture positioning feature, reference may be made to the description of the structure for projecting the second projection feature and the first posture positioning feature, which will not be repeated here.

Exemplarily, FIG. 13 schematically shows a schematic diagram of realizing the positioning of the measurement posture based on an imaging method according to an embodiment of the present disclosure. In FIG. 13 , the first posture positioning feature is set on the object to be measured.

According to an embodiment of the present disclosure, the method may further include the following operations.

If the measurement probe is set at a position corresponding to the measurement area, in a case where it is determined that the current measurement posture is not the target measurement posture, the second posture positioning feature is determined. According to the second posture positioning feature, the current measurement posture is adjusted to the target measurement posture.

According to an embodiment of the present disclosure, if the measurement probe is set at a position corresponding to the measurement area, if it is determined that the current measurement posture is not the target measurement posture, the re-measurement posture positioning described above needs to be performed. That is, after completing the positioning of the measurement area, if the current measurement posture is not the target measurement posture, it is necessary to perform the above-mentioned re-measurement posture positioning. The current measurement posture may be adjusted according to the second posture positioning feature until the current measurement posture is the target measurement posture. The second gesture location feature may be the same as or different from the first gesture location feature.

According to an embodiment of the present disclosure, adjusting the current measurement posture to the target measurement posture according to the second posture positioning feature may include the following operations.

Get the third projected feature. If it is determined that the second posture locating feature does not match the third projection feature, the current measurement posture is adjusted until the second posture locating feature matches the third projection feature. When it is determined that the second posture positioning feature matches the third projection feature, it is determined that the current measurement posture is the target measurement posture.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement posture positioning, an optical method can be adopted, that is, the second posture positioning feature is matched with the third projection feature, and the target measurement posture is determined according to the matching result, wherein , the third projection feature is formed according to an optical method, that is, a light spot with a preset shape is projected by the light source to form the third projection feature, and the shape of the light spot can be determined according to the second posture positioning feature. That is, for the measured object, set the matching third projection feature according to the second posture positioning feature, so that the current measurement posture that the second posture positioning feature matches with the third projection feature is the target measurement posture.

According to an embodiment of the present disclosure, the structure for projecting the third projection feature may be provided on the object to be measured, the measurement probe, the mount, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The second posture positioning feature may be provided on at least one of the measuring probe, the fixing base, the object to be measured, and other objects. The adjustment process based on the optical method will be described below from two angles of the setting position of the structure for projecting the third projection feature and the setting position of the second posture positioning feature.

Described from the perspective of the setting position of the structure for projecting the third projection feature.

First, if the structure for projecting the third projection feature is arranged on the measured object, the second posture positioning feature can be arranged on at least one of the measured object, the measuring probe, the fixed seat and other objects.

Second, if the structure for projecting the third projection feature is set on the measuring probe, the second posture positioning feature cannot be set on the measuring probe and the holder, but can be set on the measured object or other objects, because the After being set at the position corresponding to the measurement area, the probe head is set on the fixed seat.

Thirdly, if the structure for projecting the third projection feature is set on the fixed seat, the second posture positioning feature cannot be set on the measuring probe and the fixed base, but can be set on the measured object or other objects. It is also caused by the fact that after the measuring probe is set at the position corresponding to the measurement area, the probe probe is set on the fixed seat.

Fourth, if the structure for projecting the third projection feature is set on other objects, the second posture positioning feature can be set on at least one of the measured object, the measuring probe, the fixed seat and other objects. It should be noted that, if the second posture positioning feature is set on other objects, the positioning of the measurement posture can be realized by the following method, that is, when it is determined that the second posture positioning feature does not match the third projection feature, the current measurement posture is adjusted. , until the second posture positioning feature matches the third projection feature, and when it is determined that the second posture positioning feature matches the third projection feature, the current measurement posture is determined as the target measurement posture. The matching between the second posture positioning feature and the third projection feature mentioned here means that the second posture positioning feature is blocked by the measured object, so that the third projection feature cannot be projected to the position where the second posture positioning feature is located. If the matching of the positioning feature and the third projection feature does not match, there is at least one third projection feature that can be projected to the position where the second posture positioning feature is located.

From the perspective of the setting position of the second posture positioning feature.

First, if the second posture positioning feature is arranged on the object to be measured, the structure for projecting the third projection feature can be arranged on the object to be measured, a measuring probe, a fixed seat or other objects.

Second, if the second posture positioning feature is set on the measuring probe, the structure for projecting the third projection feature is separate from the measuring probe and the fixed seat, and can be set on the object to be measured or other objects. After the probe is set at the position corresponding to the measurement area, the probe probe is set on the fixed seat.

Thirdly, if the second posture positioning feature is arranged on the fixed seat, the structure for projecting the third projection feature is separate from the measurement probe and the fixed seat, and can be arranged on the measured object or other objects. It is also caused by the fact that after the measuring probe is set at the position corresponding to the measurement area, the probe probe is set on the fixed seat.

Fourth, if the second posture positioning feature is set on other objects, the structure for projecting the third projection feature can be set on the measured object, the measuring probe, the fixed seat or other objects. It should be noted that, if the structure for projecting the third projection feature is set on another object, please refer to the description of the corresponding part above, which will not be repeated here.

The positioning of the measurement posture is realized by an optical method. On the one hand, since the position and angle of the light source can be flexibly adjusted, it can be easily matched with the second posture positioning feature. Therefore, the second posture positioning feature can be flexibly set, thereby reducing the The difficulty of setting the feature of the second pose location. On the other hand, by adjusting the shape of the outgoing light spot, the matching with the second posture positioning feature can be better achieved, and the positioning accuracy can be improved.

A fifth target image is acquired. A third template image is acquired, wherein the third template image includes the second gesture location feature. When it is determined that the fifth target image does not match the third template image, the current measurement posture is adjusted to acquire a new fifth target image until the new fifth target image matches the third template image. When it is determined that the new fifth target image matches the third template image, the current measurement posture is determined to be the target measurement posture.

According to the embodiment of the present disclosure, in order to ensure the flexibility of use and the accuracy of the measurement posture positioning, an image matching method can be used, that is, the fifth target image is matched with the third template image, and the target measurement posture is determined according to the matching result. Wherein, the third template image may include the second posture positioning feature and the position of the second posture positioning feature in the third template image is a preset position. In the process of matching the fifth target image with the third template image, the fifth target image may be a target image that does not include the second posture positioning feature, or may include the second posture positioning feature but the second posture positioning feature is in the fifth target image. The position of the target image is not the target image at the preset position, and may also be a target image including the second posture positioning feature and the position of the second posture positioning feature is the preset position at the position of the fifth target image. Since the third template image includes the second gesture positioning feature located at the preset position, if the fifth target image matches the third template image, it can be explained that the fifth target image includes the second gesture positioning feature and the second gesture positioning feature The position in the fifth target image is a preset position. In other words, the purpose of matching the fifth target image with the third template image is to make the acquired fifth target image include the second posture positioning feature and the position of the second posture positioning feature in the fifth target image is a predetermined set location.

According to the embodiment of the present disclosure, in the case where it is determined that the fifth target image matches the third template image, it can be stated that the current measurement posture is the target measurement posture.

According to an embodiment of the present disclosure, the structure for acquiring the fifth target image may be disposed on the object to be measured, the measurement probe, the fixed seat or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The second posture positioning feature may be provided on at least one of the measuring probe, the fixing base, the object to be measured, and other objects. For the description of the structure for acquiring the fifth target image and the second posture positioning feature, reference may be made to the description of the structure for projecting the third projection feature and the second posture positioning feature, which will not be repeated here. The difference is that if the structure for acquiring the fifth target image is provided on the measurement probe, the second posture positioning feature may be provided on at least one of the measured object, the measurement probe, the fixed seat and other objects. If the structure for capturing the fifth target image is provided on the fixed seat, the second posture positioning feature may be provided on at least one of the measured object, the measurement probe, the fixed seat and other objects.

A sixth target image is acquired, wherein the sixth target image includes the second gesture positioning feature. If it is determined that the position of the second posture positioning feature in the sixth target image is not at the third preset position, adjust the current measurement posture to obtain a new sixth target image until the second posture is positioned in the new sixth target image The location of the feature is at the third preset location. When it is determined that the position of the second posture positioning feature in the new sixth target image is at the third preset position, the current measurement posture is determined as the target measurement posture.

According to the embodiments of the present disclosure, in order to ensure the flexibility of use and the accuracy of measuring posture positioning, an imaging method can be used, that is, if the position of the second posture positioning feature in the sixth target image is the third preset position, it can be It indicates that the positioning of the measurement pose is completed.

According to the embodiment of the present disclosure, the second process of using the imaging method to measure the posture positioning is the process of determining whether the position of the second posture positioning feature in the sixth target image is the third preset position. The position in the sixth target image is not the third preset position, then the current measurement posture can be adjusted to obtain a new sixth target image, until the position of the second posture positioning feature in the new sixth target image is the third Preset position. In the case where the position of the second posture positioning feature in the new sixth target image is the third preset position, it can be explained that the current measurement posture is the target measurement posture.

According to an embodiment of the present disclosure, the structure for acquiring the sixth target image may be disposed on the object to be measured, the measurement probe, the fixed seat, or other objects. The other objects may represent objects other than the measurement probe, the fixture, and the object to be measured. The second posture positioning feature may be provided on at least one of the measuring probe, the fixing base, the object to be measured, and other objects. For the description of the structure for acquiring the sixth target image and the second posture positioning feature, reference may be made to the description of the structure for projecting the third projection feature and the second posture positioning feature, which will not be repeated here.

Prompt information is generated, wherein the prompt information is used to prompt that the measurement posture positioning and/or the measurement area positioning is completed, and the form of the prompt information includes at least one of image, voice or vibration.

According to the embodiments of the present disclosure, in order for the user to know in time whether the positioning of the measurement posture and/or the positioning of the measurement area is completed, prompt information may be generated after the positioning of the measurement posture and/or the positioning of the measurement area is completed. Wherein, the specific expression form of the prompt information may include at least one of image, voice and vibration.

When it is determined that the fixing seat is installed at the position corresponding to the measurement area and the measurement probe is not installed in the fixing portion, the measurement probe is installed on the fixing seat. When it is determined that the fixing seat is not arranged at the position corresponding to the measurement area, the fixing seat is arranged at the position corresponding to the measurement area through the first fitting, and the measuring probe is arranged on the fixing seat.

According to the embodiment of the present disclosure, if the measurement probe is set at a position corresponding to the measurement area through the fixing seat, during the tissue composition measurement process, the fixing seat can be separated from the measurement area, and the measurement probe can be separated from the fixing seat. If the fixing base is not set at the position corresponding to the measurement area, the fixing base can be set at the position corresponding to the measurement area through the first fitting, and the measuring probe can be set at the fixing base. If the fixing base is set at the position corresponding to the measurement area and the measuring probe is not set on the fixing base, the measuring probe can be set at the fixing base.

Exemplarily, for short-term measurement at any time, the fixing base can be arranged at a position corresponding to the measurement area, the measuring probe can be separated from the fixing base, and the measuring probe can be arranged on the fixing base when measurement is required. For long-term measurement, the fixing seat can be separated from the measurement area, and the measuring probe can be separated from the fixing seat. When measurement is required, the fixing seat is set at the position corresponding to the measurement area through the first fitting, and the measuring probe is set on the fixing seat.

When it is determined that the measurement probe is not arranged at the position corresponding to the measurement area, the measurement probe is arranged at the position corresponding to the measurement area through the second fitting.

According to the embodiment of the present disclosure, if the measurement probe is directly set at the position corresponding to the measurement area, the measurement probe can be separated from the measurement area during the tissue composition measurement process, and the measurement probe can be set through the second fitting when measurement is required. at the position corresponding to the measurement area.

According to an embodiment of the present disclosure, determining the concentration of the measured tissue component according to at least one output light intensity corresponding to a preset wavelength may include the following operations.

The first output light intensity and the second output light intensity are determined from at least one output light intensity corresponding to a preset wavelength. The concentration of the measured tissue component is determined according to the first output light intensity and the second output light intensity corresponding to the preset wavelength.

According to an embodiment of the present disclosure, the average optical length of the outgoing light corresponding to the first output light intensity is different from the average optical length of the outgoing light corresponding to the second output light intensity.

According to an embodiment of the present disclosure, determining the concentration of the measured tissue component according to the first output light intensity and the second output light intensity corresponding to the preset wavelength may include the following operations.

Differential processing is performed on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal. According to the differential signal corresponding to the preset wavelength, the concentration of the measured tissue component is determined.

According to the embodiments of the present disclosure, since changes in uncontrollable measurement conditions are unpredictable and uncontrollable, it is difficult to reduce the influence of changes in uncontrollable measurement conditions on measurement results by adopting an effective control method to achieve reproducibility. In order to improve the reliability of the measurement results, the inventor found that the influence of changes in uncontrollable measurement conditions on the measurement results can be reduced by using a reasonable mathematical algorithm, so that the influence on the measurement results can be reduced to a negligible level, even if it is impossible to The influence of the variation of the controlled measurement conditions on the measurement results is comparable to the influence of random noise on the measurement results.

In order to reduce the influence of the variation of uncontrollable measurement conditions on the measurement result, an interference suppression method can be adopted, wherein the interference suppression method can include a differential measurement method. The differential measurement method may include a time differential measurement method and a position differential measurement method. The reason why the differential measurement method can reduce the influence of uncontrollable measurement conditions on the measurement results is that if the interference information carried by the output light intensities under different average optical paths is basically the same, that is, the output light intensities under different average optical paths are disturbed. The influences are basically the same, since the effective information carried by the output light intensities under different average optical paths is different, therefore, the output light intensities under the two average optical paths (that is, the first output light intensity and the second output light intensity ) to perform differential processing to obtain a differential signal, and determine the concentration of the measured tissue component according to the differential signal. Among them, the interference information can be understood as the response of the output light intensity to the interference. Effective information can be understood as the response of the output light intensity to the measured tissue composition.

According to the embodiment of the present disclosure, the differential processing in the differential processing of the first output light intensity and the second output light intensity corresponding to the preset wavelength may include a processing method in hardware and a processing method in software. Wherein, the processing manner in terms of hardware may include processing by using a differential circuit. The processing method in software may include using a difference algorithm to perform a difference operation. Differentiation algorithms may include direct differencing operations and logarithmic differencing operations. Among them, the direct difference operation refers to the difference processing of two parameters directly. The logarithmic difference operation refers to first performing the logarithmic operation on two parameters to obtain the logarithmic parameters, and then performing the difference processing of the two logarithmic parameters.

According to the embodiments of the present disclosure, the common mode interference information can be effectively attenuated by the differential measurement method, thereby improving the reliability of the measurement result.

According to an embodiment of the present disclosure, performing differential processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal may include the following operations.

A differential circuit is used to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal.

According to the embodiments of the present disclosure, a differential circuit can be used to implement differential processing of the first output light intensity and the second output light intensity, so as to directly obtain a differential signal.

A differential algorithm is used to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, using a differential algorithm to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal may include the following operations.

A direct differential operation is performed on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal.

Logarithmic processing is performed on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain the first logarithmic light intensity and the second logarithmic light intensity. Perform a direct differential operation on the first logarithmic light intensity and the second logarithmic light intensity corresponding to the preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, the first logarithmic light intensity represents the logarithm of the first output light intensity, and the second logarithmic light intensity represents the logarithm of the second output light intensity.

The differential signal can be determined by the following formula (1).

Among them, A _D represents the differential signal,

represents the first output light intensity,

Indicates the second output light intensity.

represents the average optical path corresponding to the first output light intensity,

represents the average optical path length corresponding to the second output light intensity.

According to an embodiment of the present disclosure, determining the concentration of the measured tissue component according to the differential signal corresponding to the preset wavelength may include the following operations.

The differential signal corresponding to the preset wavelength is input into the first tissue component concentration prediction model, and the concentration of the measured tissue component is output.

According to an embodiment of the present disclosure, the first tissue component concentration prediction model may be generated based on training of a chemometric model, wherein the chemometric model may include a regression model. The regression model may include a linear regression model, and the linear regression model may include a univariate linear regression model.

According to an embodiment of the present disclosure, a first training sample set is obtained, wherein the first training sample set includes a plurality of first training samples, wherein each first training sample includes a first true concentration of a measured tissue component and a A differential signal corresponding to a true concentration. According to the first training sample set, a first tissue component concentration prediction model is established.

According to an embodiment of the present disclosure, the first tissue component concentration prediction model may be generated by obtaining a first training sample set, where the first training sample set includes a plurality of first training samples, and the first training samples include The first real concentration and the differential signal corresponding to the first real concentration, using the differential signal corresponding to the first real concentration as an input variable, and using the first real concentration as an output variable, train the mathematical model to be trained, and obtain the first tissue component Concentration prediction model.

According to an embodiment of the present disclosure, establishing the first tissue component concentration prediction model according to the first training sample set may include the following operations.

The first training sample set is preprocessed to obtain the processed first training sample set. According to the processed first training sample set, a first tissue component concentration prediction model is established.

According to the embodiments of the present disclosure, in order to improve the prediction accuracy of the model, the first training sample set may be preprocessed to determine abnormal training samples in the first training sample set, so as to establish a model based on the first training sample set after deleting the abnormal training samples A first tissue component concentration prediction model.

When the fourth preset condition is satisfied, the first tissue component concentration prediction model is modified to process the new differential signal using the revised first tissue component concentration prediction model to obtain a new measured tissue component concentration.

According to the embodiment of the present disclosure, in order to improve the prediction accuracy of the model, it is necessary to adjust the first tissue component concentration prediction model according to the actual conditions in the tissue component measurement process. The first tissue component concentration prediction model is revised to obtain a revised first tissue component concentration prediction model. Wherein, the fourth preset condition may include that the time interval between the current tissue component measurement and the establishment of the first tissue component concentration prediction model is less than or equal to the time threshold and/or the state of the measured object has not changed significantly, the measured object The state may include the physical state of the subject and/or the skin state of the subject, such as skin burns.

Usually in a relatively short period of time or the state of the measured object does not change significantly, the inapplicability of the first tissue component concentration prediction model caused by the changes in the tissue composition of the measured object and the state of the measurement device can be determined by analyzing the first tissue component. The component concentration prediction model was revised to solve.

After obtaining the revised first tissue component concentration prediction model, a new difference signal may be obtained, input the new difference signal into the revised first tissue component concentration prediction model, and output a new measured tissue component concentration.

According to an embodiment of the present disclosure, modifying the first tissue component concentration prediction model may include the following operations.

Obtain the first target concentration of the measured tissue component. A differential signal corresponding to the first target concentration is acquired. The first tissue component concentration prediction model is corrected based on the difference signal corresponding to the first target concentration and the first target concentration.

According to an embodiment of the present disclosure, the first tissue component concentration prediction model may be generated by training based on a univariate linear regression model. Since the two input parameters of the univariate linear regression model include the slope and the intercept, the model training process is to determine the slope and intercept. If the fourth preset condition is satisfied, it is found according to the research that the slope of the first tissue concentration prediction model remains unchanged but the intercept changes. In this case, the intercept needs to be re-determined. The target concentration and the differential signal corresponding to the first target concentration are used to modify the first tissue component concentration prediction model to obtain a new intercept, and further obtain the revised first tissue component concentration prediction model.

Under the condition that the fifth preset condition is satisfied, the new differential signal is processed by using the new first tissue component concentration prediction model to obtain a new measured tissue component concentration.

According to the embodiments of the present disclosure, in order to improve the prediction accuracy of the model, it is necessary to determine whether a new first tissue component concentration prediction model needs to be re-established according to the actual conditions in the tissue component measurement process, that is, if the actual conditions satisfy the fifth preset condition , a new first tissue component concentration prediction model can be established. Wherein, the fifth preset condition may include that the time interval between the current tissue component measurement and the establishment of the first tissue component concentration prediction model is greater than the time threshold and/or the state of the measured object changes greatly, and the state of the measured object may Including the physical condition of the subject and/or the skin condition of the subject, such as skin burns.

The reason for adopting the above method is that, usually in a long period of time or the state of the measured object changes greatly, the tissue composition of the measured object and the state of the measuring device change greatly, so that the original first tissue component concentration The prediction model is no longer applicable, and cannot be applied by modifying the original first tissue component concentration prediction model, and a new first tissue component concentration prediction model needs to be re-established.

According to an embodiment of the present disclosure, a new first tissue component concentration prediction model may be generated by obtaining a new first training sample set, wherein the new first training sample set includes a plurality of new first training samples, Wherein, each new first training sample includes a new first true concentration of the measured tissue component and a differential signal corresponding to the new first true concentration, and a new first training sample set is established according to the new first training sample set Tissue component concentration prediction models.

Obtain the current interference parameter value of each interference parameter in the plurality of interference parameters. The plurality of current interference parameter values and the differential signal corresponding to the preset wavelength are input into the second tissue component concentration prediction model, and the concentration of the measured tissue component is output.

According to the embodiments of the present disclosure, since the process of measuring the concentration of tissue components is also affected by interference parameters, wherein the interference parameters may include temperature and pressure, etc. Therefore, in order to improve the reliability of the measurement results, an interference-based parameter may be established. Parameter of the second tissue component concentration prediction model.

Using the second tissue component concentration prediction model to process multiple current interference parameter values and differential signals corresponding to preset wavelengths to obtain the measured tissue component concentration, which may include inputting multiple current interference parameter values into the second tissue component concentration prediction model , output a differential interference signal, use the differential interference signal to correct the differential signal corresponding to the preset wavelength, obtain a correction signal corresponding to the preset wavelength, and determine the concentration of the measured tissue component according to the correction signal corresponding to the preset wavelength.

According to the embodiments of the present disclosure, by establishing the second tissue component concentration prediction model based on the interference parameter to predict the tissue component concentration, the reliability of the measurement result is further improved.

Acquiring a second training sample set, wherein the second training sample set includes a plurality of second training samples, wherein each second training sample includes a second true concentration of the measured tissue component and a differential signal corresponding to the second true concentration . Obtain a third training sample set, wherein the third training sample set includes a plurality of third training samples, wherein each third training sample includes a training interference parameter value of each interference parameter in the plurality of interference parameters and a The differential signal corresponding to the interference parameter value. According to the second training sample set, a prediction model for the concentration of tissue components to be corrected is established. According to the third training sample set, a correction parameter model is established. According to the tissue component concentration prediction model to be corrected and the correction parameter model, a second tissue component concentration prediction model is obtained.

According to an embodiment of the present disclosure, the correction parameter model is a mathematical model between the interference parameter and the differential signal corresponding to the interference parameter. The tissue component concentration prediction model to be corrected is a mathematical model between the tissue component concentration and the differential signal corresponding to the tissue component concentration. Obtaining and establishing the second tissue component concentration prediction model according to the tissue component concentration prediction model to be corrected and the correction parameter model may include obtaining a differential signal corresponding to the interference parameter according to the correction parameter model, and using the differential signal corresponding to the interference parameter to pair the tissue component concentration with the tissue component concentration. The corresponding differential signal is corrected, and a second tissue component concentration prediction model is established according to the tissue component concentration and the corrected differential signal. In the model training process, the tissue component concentration is the second real concentration, and the differential signal corresponding to the tissue component concentration is the differential signal corresponding to the second real concentration.

According to the embodiments of the present disclosure, in order to improve the prediction accuracy of the model, both the second training sample set and the third training sample set may be preprocessed to determine abnormal training samples in the second training sample set and abnormal training samples in the third training sample set The training samples are used to establish a prediction model for the concentration of tissue components to be corrected according to the second training sample set after the abnormal training samples are deleted. A correction parameter model is established according to the third training sample set after removing abnormal samples.

Under the condition that the fourth preset condition is satisfied, the second tissue component concentration prediction model is revised, so as to use the revised second tissue component concentration prediction model to process the new differential signal and the new multiple current interference parameter values to obtain Concentrations of new tested tissue components.

According to the embodiments of the present disclosure, in order to improve the prediction accuracy of the model, it is necessary to adjust the second tissue component concentration prediction model according to the actual conditions in the tissue component measurement process. The second tissue component concentration prediction model is revised to obtain a revised second tissue component concentration prediction model. Wherein, the fourth preset condition may include that the time interval between the current tissue component measurement and the establishment of the second tissue component concentration model is less than or equal to the time threshold and/or the state of the measured object has not changed significantly, the measured object’s state The state may include the physical state of the subject and/or the skin state of the subject, such as skin burns.

Usually in a relatively short period of time or the state of the measured object does not change greatly, the inapplicability of the second tissue component concentration prediction model caused by the change of the tissue composition of the measured object and the state change of the measuring device can be determined by applying the second Tissue component concentration prediction model revisions to address.

After obtaining the revised second tissue component concentration prediction model, a new differential signal and new multiple current interference parameter values can be obtained, and the new differential signal and new multiple current interference parameter values can be input into the revised second tissue component concentration prediction model. The tissue component concentration prediction model outputs the new measured tissue component concentration.

According to an embodiment of the present disclosure, modifying the second tissue component concentration prediction model may include the following operations.

Obtain a second target concentration of the measured tissue component. A differential signal corresponding to the second target concentration is acquired. Obtain the current interference parameter value of each interference parameter in the multiple interference parameters. The second tissue component concentration prediction model is modified according to the second target concentration, the plurality of interference parameter values, and the differential signal corresponding to the second target concentration.

According to an embodiment of the present disclosure, the second tissue component concentration prediction model may be generated by training based on a univariate linear regression model. Since the two input parameters of the univariate linear regression model include the slope and the intercept, the model training process is to determine the slope and intercept. If the first preset condition is met, it is found according to the research that the slope of the second tissue concentration prediction model remains unchanged but the intercept changes. In this case, the intercept needs to be re-determined. The target concentration, the differential signal corresponding to the second target concentration, and the multiple interference parameter values are used to modify the second tissue component concentration prediction model to obtain a new intercept, and further obtain the revised second tissue component concentration prediction model.

Under the condition that the fifth preset condition is satisfied, the new differential signal and the new multiple current interference parameter values are processed by using the new second tissue component concentration prediction model to obtain a new measured tissue component concentration.

According to the embodiments of the present disclosure, in order to improve the prediction accuracy of the model, it is necessary to determine whether a new second tissue component concentration prediction model needs to be re-established according to the actual conditions in the tissue component measurement process, that is, if the actual conditions satisfy the fifth preset condition , a new prediction model for the concentration of the second tissue component can be established. Wherein, the fifth preset condition may include that the time interval between the current tissue component measurement and the establishment of the second tissue component concentration model is greater than the time threshold and/or the state of the measured object has changed greatly, and the state of the measured object may include The physical condition of the subject and/or the skin condition of the subject, such as skin burns.

The reason for adopting the above method is that usually in a long time or the state of the measured object changes greatly, the tissue composition of the measured object and the state of the measuring device change greatly, so that the original concentration of the second tissue component The prediction model is no longer applicable, and cannot be adapted by modifying the original second tissue component concentration prediction model, and a new second tissue component concentration prediction model needs to be re-established.

According to an embodiment of the present disclosure, a new second tissue component concentration prediction model may be generated by obtaining a new second training sample set, wherein the new second training sample set includes a plurality of new second training samples, Wherein, each new second training sample includes a new second true concentration of the measured tissue component and a differential signal corresponding to the new true concentration. Obtain a new third training sample set, wherein the new third training sample set includes a plurality of new third training samples, wherein each new third training sample includes a new value of each interference parameter of the plurality of interference parameters. and the differential signal corresponding to each new training disturbance parameter value. According to the new second training sample set, a new tissue component concentration prediction model to be corrected is established. According to the new third training sample set, a new correction parameter model is established. According to the new tissue component concentration prediction model to be corrected and the new correction parameter model, a new second tissue component concentration prediction model is obtained.

According to the embodiment of the present disclosure, the first output light intensity and the second output light intensity are collected by the same or different photosensitive surfaces of the same type at different times, wherein the first output light intensity is the systolic light intensity, and the second output light intensity is The light intensity is the light intensity in the diastolic period, and the same photosensitive surface includes one or more photosensitive surfaces, and the same photosensitive surface is used to output one output light intensity.

According to the embodiments of the present disclosure, when the first output light intensity and the second output light intensity are collected by the same or different photosensitive surfaces of the same type at different times, a pulse wave-based time difference measurement method can be used to measure tissue composition Measurement.

Pulse is the arterial pulsation, which refers to the periodic contraction and relaxation with the beating of the heart. The pressure in the aorta causes pulsatile changes in the diameter of the blood vessels, and the blood flow in the blood vessels also changes regularly and periodically. Each pulse waveform includes an ascending branch and a descending branch, where the ascending branch represents the dilation of the ventricular systolic artery and the descending branch represents the ventricular diastolic arterial retraction. A single contraction of the ventricle represents a pulsatile cycle.

According to the embodiments of the present disclosure, since the pulse wave-based time difference measurement method is adopted, it is necessary to utilize the pulse information as much as possible. Therefore, in order to improve the reliability of the measurement result, the photosensitive surface can be set as close as possible to the target part (for example, the target blood vessels) location. That is, the same photosensitive surfaces for outputting the first output light intensity and the second output light intensity can be set at a position where the distance from the target site is less than or equal to the fourth distance threshold. Wherein, the fourth distance threshold can be zero, that is, the same photosensitive surface can be set on the target part. The same type of photosensitive surface used to output the first output light intensity and the second output light intensity is set at a position where the distance from the target site is less than or equal to the fourth distance threshold, that is, used for outputting the first output light intensity and the second output light intensity The distance between each photosensitive surface of the same strong photosensitive surface and the target site is less than or equal to the fourth distance threshold. The distance between each photosensitive surface of the same photosensitive surface and the target site is less than or equal to the fourth distance threshold, which may be the distance between the edge of the photosensitive surface farthest from the target site and the target blood vessel in the same photosensitive surface is less than or equal to the fourth distance threshold.

It should be noted that using the pulse wave-based time difference measurement method, it is not contradictory to use the pulse information as much as possible and the above-mentioned use of a large-area photosensitive surface to reduce the adverse effects of pulse beating on the measurement. It is possible to utilize useful information from the pulse beat, which minimizes the adverse effects of the pulse beat. In addition, the first output light intensity may also be the diastolic light intensity, and the second output light intensity may also be the systolic light intensity. The first output light intensity and the second output light intensity corresponding to the preset wavelength may be the output light intensity in the same pulsation period, or may be the output light intensity in different pulsation periods.

According to the embodiment of the present disclosure, the first output light intensity corresponding to the preset wavelength is collected by a first photosensitive surface of the same type corresponding to the preset wavelength, and the second output light intensity corresponding to the preset wavelength is Set the wavelength corresponding to the second photosensitive surface of the same type to be collected, wherein the first photosensitive surface of the same type includes one or more photosensitive surfaces, and the second similar photosensitive surface includes one or more photosensitive surfaces.

According to an embodiment of the present disclosure, for a preset wavelength, there are a first photosensitive surface of the same type and a second photosensitive surface of the same type corresponding to the preset wavelength, wherein the first photosensitive surface of the same type is used to output the first photosensitive surface corresponding to the preset wavelength. For an output light intensity, the second photosensitive surface of the same type is used for outputting a second output light intensity corresponding to the preset wavelength. Both the first homogeneous photosensitive surface and the second homogeneous photosensitive surface may include one or more photosensitive surfaces.

According to an embodiment of the present disclosure, the first output light intensity and the second output light intensity may be processed using a position differential measurement method to determine the concentration of the measured tissue component.

According to the embodiment of the present disclosure, since the position difference measurement method needs to avoid the target part (for example, the target blood vessel) as much as possible, in order to improve the reliability of the measurement result, the photosensitive surface can be set as far as possible from the target part. That is, the first similar photosensitive surface for outputting the first output light intensity can be set at a position where the distance from the target site is greater than or equal to the fifth distance threshold, that is, each photosensitive surface of the first similar photosensitive surface is located at a distance from the target site. The distance is greater than or equal to the fifth distance threshold. The distance between each photosensitive surface of the first similar photosensitive surface and the target site is greater than or equal to the fifth distance threshold, which may be the distance from the edge of the photosensitive surface closest to the target site in the first similar photosensitive surface to the target site is greater than or equal to the fifth distance threshold. Five distance thresholds. Alternatively, the photosensitive surfaces of the first similar type are not in contact with the target portion, and the distance from the center of the photosensitive surface closest to the target portion in the first similar photosensitive surfaces to the target portion is greater than or equal to the fifth distance threshold. The photosensitive surface for outputting the second output light intensity is set at a position whose distance from the target site is greater than or equal to a sixth distance threshold. For the understanding that the second same type of photosensitive surface for outputting the second light intensity is arranged at a position with a distance from the target site greater than or equal to the sixth distance threshold, please refer to the first similar photosensitive surface for outputting the first output light intensity description, which will not be repeated here.

According to the embodiment of the present disclosure, the first photosensitive surface of the same type and the second photosensitive surface of the same type are the same photosensitive surface, and the outgoing light received by the first photosensitive surface and the second photosensitive surface of the same type is the incident light incident from different incident positions through the transmitted.

According to an embodiment of the present disclosure, the first photosensitive surface of the same kind and the second photosensitive surface of the same kind are different photosensitive surfaces of the same kind.

According to the embodiment of the present disclosure, since the incident position of the incident light may include at least one, if the incident position of the incident light includes at least two, the first photosensitive surface of the same kind and the second photosensitive surface of the second kind may be the same photosensitive surface, so The difference is that if the same type of photosensitive surface is used to receive the outgoing light corresponding to the first output light intensity, that is, it is used as the first photosensitive surface of the same type, the incident position of the outgoing light is the first incident position. If the photosensitive surface of the same type is the same photosensitive surface used to receive the outgoing light corresponding to the second output light intensity, that is, it is used as the second photosensitive surface of the same type, the incident position of the outgoing light is the second incident position, and the first incident light The position and the second incident position are different incident positions.

According to an embodiment of the present disclosure, the first photosensitive surface of the same type and the second photosensitive surface of the same type may also be different photosensitive surfaces of the same type.

According to an embodiment of the present disclosure, the average optical path length of the outgoing light received by different photosensitive positions of each photosensitive surface of the first same type of photosensitive surface belongs to the first average optical path range, wherein the first average optical path range is based on the first The optical path average value is determined, and the first optical path average value is an average value calculated according to the average optical path length of the outgoing light received by each photosensitive position of the first photosensitive surface of the same type. The average optical length of the outgoing light received by different photosensitive positions of each photosensitive surface of the second same type of photosensitive surface belongs to the second average optical path range, wherein the second average optical path range is determined according to the average value of the second optical path, Wherein, the average value of the second optical path is an average value calculated according to the average optical path length of the outgoing light received by each photosensitive surface of the second same type of photosensitive surface.

According to the embodiments of the present disclosure, in order to improve the reliability of the measurement results of the tissue composition measurement using the position difference measurement method, it is necessary to try to ensure that the outgoing light received by the first photosensitive surface has the characteristics of a short optical path, and the second photosensitive surface has the characteristics of short optical path. The outgoing light received by the surface also has the characteristics of a short optical path. The short optical path can be understood as the average optical path of the outgoing light within the range of the average optical path.

For the first same type of photosensitive surface, the average optical path length of the outgoing light received by different photosensitive positions of each photosensitive surface in the first same type of photosensitive surface belongs to the first average optical path range. Wherein, the first average optical path range is determined in the following manner. The first optical path average value of the average optical path lengths of the outgoing light received by the respective photosensitive positions of the first same type of photosensitive surfaces is determined, and the variation range of the first optical path is determined. The first average optical path range is determined according to the first optical path average value and the first optical path variation range. Exemplarily, if the average value of the first optical path is b and the variation range of the first optical path is ±40%, the first average optical path range may be greater than or equal to 0.6b and less than or equal to 1.4b.

For the second same type of photosensitive surface, the average optical length of the outgoing light received by different photosensitive positions of each photosensitive surface in the second same type of photosensitive surface belongs to the second average optical length range. Wherein, the second average optical path range is determined in the following manner. The second optical path average value of the average optical path lengths of the outgoing light received by the respective photosensitive positions of the second same type of photosensitive surfaces is determined, and the variation range of the second optical path is determined. The second average optical path range is determined according to the second optical path average value and the second optical path variation range.

According to an embodiment of the present disclosure, the absolute value of the difference between the first optical path average value and the second optical path average value belongs to the first optical path difference range.

According to the embodiments of the present disclosure, in order to improve the reliability of the measurement result obtained by the tissue composition measurement based on the differential measurement method, it is necessary to set the first photosensitive surface of the same type and the second photosensitive surface of the same type within a suitable position range. The following description will be given by taking the measured tissue component as blood glucose as an example. If the measured tissue component is blood glucose, the target tissue layer is the dermis layer, and the required output light intensity is the output light intensity that mainly carries the tissue component information in the dermis layer.

First, if the distance between the position of the photosensitive surface and the center of the incident light is too small, the output light intensity of the outgoing light will mainly carry the tissue composition information in the epidermis layer. If the distance between the position of the photosensitive surface and the center of the incident light is too large, the output light intensity of the outgoing light will mainly carry the tissue composition information in the subcutaneous fat layer. The dermis layer is located between the epidermis layer and the subcutaneous fat layer. It can be seen that the setting positions of the first and second similar photosensitive surfaces need to be selected within an appropriate range of positions. The first and second similar photosensitive surfaces The distance between the faces should not be too large.

Second, although the differential measurement method can effectively weaken the common mode interference, the differential measurement method will also lose a part of effective information, that is, blood glucose information, while weakening the common mode interference. If the two locations are extremely close, the useful information may be completely lost. It can be seen that the setting positions of the first and second similar photosensitive surfaces need to be selected within a suitable position range, and the distance between the first and second similar photosensitive surfaces cannot be too small.

In order to realize the setting of the first photosensitive surface and the second photosensitive surface of the same type within a reasonable position range, it can be determined according to the principle of effective information measurement, the principle of differential measurement precision optimization and the principle of effective elimination of interference signals. The principle of effective information measurement may refer to the fact that the outgoing light at the two positions can carry as much tissue composition information in the target tissue layer as possible, therefore, the two positions should be within a reasonable position range. The principle of precision optimization of differential measurement can mean that there should be a certain distance between two positions to ensure that as much valid information as possible remains after the difference. The principle of effective interference signal elimination can mean that the distance between two locations should be as small as possible to improve the effect of the differential measurement method in eliminating common mode interference.

Set the first photosensitive surface of the same type and the second photosensitive surface of the same type within a reasonable range, which is reflected in the optical path, that is, the average value of the first optical path corresponding to the first photosensitive surface and the corresponding photosensitive surface of the second similar type. The absolute value of the difference between the second optical path average values belongs to the first optical path difference range. Wherein, the first optical path difference range is determined according to the optimal differential optical path. The optimal differential optical path may be determined according to at least one of the above three principles.

It can be understood that the position setting requirements for the first similar photosensitive surface and the second similar photosensitive surface also require that the area of the photosensitive surface should not be too large, otherwise the differential effect will be affected, thereby affecting the reliability of the measurement results.

According to an embodiment of the present disclosure, the first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

According to the embodiments of the present disclosure, in order to set the first photosensitive surface and the second photosensitive surface of the same type within a reasonable range as far as possible, it is also necessary to ensure that the first average optical path range is less than or equal to the first optical path as far as possible, as reflected in the optical path. difference range, and the second average optical path range is less than or equal to the first optical path difference range. Therefore, the absolute value of the difference between the average value of the first optical path corresponding to the first photosensitive surface of the same type and the average value of the second optical path corresponding to the second photosensitive surface of the same type belongs to the first optical path difference range, the first average optical path range is less than or equal to the first optical path difference range, and the second average optical path range is less than or equal to the first optical path difference range.

According to an embodiment of the present disclosure, the first optical path difference range is determined according to the optimal differential optical path corresponding to the preset wavelength.

According to the embodiments of the present disclosure, when the measurement area of the measured object is determined, there is an optimal differential sensitivity corresponding to the preset wavelength, wherein the optimal differential sensitivity may represent a difference caused by a unit concentration change of the measured tissue component The sensitivity when the signal changes the most, the optimal differential optical path can be determined according to the optimal differential sensitivity, that is, the optimal differential optical path can be determined according to the principle of differential measurement precision optimization, thus, the optical path corresponding to the optimal differential sensitivity can be determined called the optimal differential optical path.

According to the embodiments of the present disclosure, after determining the optimal differential optical path corresponding to the preset wavelength, the up and down adjustment range can be set, and according to the optimal differential optical path corresponding to the preset wavelength and the up and down adjustment amplitude, The corresponding first optical path difference range.

According to the embodiment of the present disclosure, the source-detection distance of each photosensitive surface of the first same type of photosensitive surfaces corresponding to the preset wavelength from the center of the incident light is within the range of the preset source-detection distance corresponding to the preset wavelength, wherein the preset It is assumed that the source-detection distance range is determined according to the source-detection distance from the floating reference position corresponding to the preset wavelength to the center of the incident light.

According to the embodiments of the present disclosure, in order to further improve the reliability of the measurement result, the position of the photosensitive surface may be set based on the floating reference method. Among them, the floating reference method will be described as follows.

For the measured object, when the incident light enters the tissue, absorption and scattering will occur. The absorption will directly lead to the attenuation of light energy, and the scattering will affect the distribution of the outgoing light by changing the direction of photon transmission. The distribution is the result of the combined action of the two. Based on the floating reference method, for the measured tissue composition, there is a certain position from the center of the incident light. At this position, the output light intensity of the outgoing light is affected by absorption and scattering to the same extent but in opposite directions. , resulting in the outgoing light being insensitive to changes in the concentration of the measured tissue components. A position with the above characteristics can be called a reference position (or a reference position). The output intensity of the outgoing light at the reference position reflects the response to disturbances other than the measured tissue composition during the measurement. At the same time, for the measured tissue component, there is also a certain position from the center of the incident light, at which the output light intensity of the outgoing light has a sensitivity to the concentration change of the measured tissue component greater than or equal to the sensitivity threshold. A position having the above characteristics can be called a measurement position. The output light intensity of the outgoing light at the measurement location reflects the response to the measured tissue component during the measurement process, as well as the response to other disturbances other than the measured tissue component. Also, the reference position and the measurement position vary depending on the wavelength, the object to be measured, and the measurement area, and thus the reference position can be called a floating reference position.

According to the embodiments of the present disclosure, since the output light intensity of the outgoing light emitted at the floating reference position mainly carries the response to other disturbances other than the measured tissue components in the measurement process, the light emitted from the floating reference position can be The output light intensity of the outgoing light is introduced into the differential measurement to minimize common-mode interference and minimize the loss of useful information. Based on the above, when the measurement area of the measured object is determined, for the preset wavelength, at least one of the M photosensitive surfaces has a source-detection distance from the center of the incident light within the preset source corresponding to the preset wavelength. Within the detection distance range, the preset source detection distance range is determined according to the source detection distance between the floating reference position corresponding to the preset wavelength and the center of the incident light. In the embodiment of the present disclosure, the source-detection distance of each of the photosensitive surfaces of the first same type from the center of the incident light may be within a preset source-detection distance range corresponding to a preset wavelength.

Exemplarily, for example, for the measurement area B of the measured object A, the distance between the floating reference position corresponding to the preset wavelength λ ₁ and the center of the incident light is 1.7 mm, then the preset source detector corresponding to the preset wavelength λ ₁ is 1.7 mm. The distance can range from 1.5mm to 1.9mm.

Based on the above, the same type of photosensitive surface corresponding to the reference position and the same type of photosensitive surface corresponding to the measurement position can be determined, and the output light intensity collected by the same type of photosensitive surface corresponding to the reference position is called the first output light intensity. The output light intensity collected by the same photosensitive surface corresponding to the measurement area is called the second output light intensity. Alternatively, the output light intensity collected by the same photosensitive surface corresponding to the measurement area is called the first output light intensity, and the output light intensity collected by the same photosensitive surface corresponding to the reference position is called the second output light intensity.

The third output light intensity is determined from at least one output light intensity corresponding to the preset wavelength. According to the third output light intensity corresponding to the preset wavelength, the concentration of the measured tissue component is determined.

According to the embodiments of the present disclosure, a non-differential measurement method can be used to measure tissue components, that is, the concentration of the measured tissue components can be determined according to the third output light intensity corresponding to a preset wavelength.

According to the embodiment of the present disclosure, the third output light intensity corresponding to the preset wavelength is collected by the same type of photosensitive surface corresponding to the preset wavelength, and the outgoing light received by different photosensitive positions of each photosensitive surface in the same type of photosensitive surface The difference between the average optical path and the optimal optical path corresponding to the preset wavelength belongs to the second optical path difference range.

According to the embodiments of the present disclosure, in order to improve the reliability of the measurement results, when the measurement area of the measured object is determined, for the preset wavelength, different photosensitive positions in the same photosensitive surface used for collecting the third output light intensity can be made The average optical length of the received outgoing light is close to the optimal optical length corresponding to the preset wavelength, that is, the average optical length of the outgoing light received at different photosensitive positions in the same photosensitive surface used to collect the third output light intensity and The absolute value of the optimal optical path difference corresponding to the preset wavelength is less than or equal to the second optical path difference range. The optimal optical path length corresponding to the preset wavelength can be understood as the optical path length corresponding to the maximum sensitivity of the measured tissue component under the preset wavelength.

According to an embodiment of the present disclosure, determining the concentration of the measured tissue component according to the third output light intensity corresponding to the preset wavelength may include the following operations.

The third output light intensity corresponding to the preset wavelength is input into the third tissue component concentration prediction model, and the measured tissue component concentration is output.

According to an embodiment of the present disclosure, the third tissue component concentration prediction model may be generated by obtaining a fourth training sample set, wherein the fourth training sample set includes a plurality of fourth training samples, wherein each fourth training sample Including the third true concentration of the measured tissue component and the output light intensity corresponding to the third true concentration, a third tissue component concentration prediction model is established according to the fourth training sample set.

Under the condition that the fourth preset condition is satisfied, the third target concentration of the measured tissue component is obtained, the output light intensity corresponding to the third target concentration is obtained, and according to the output light intensity corresponding to the third target concentration and the third target concentration , modifying the third tissue component concentration prediction model, so as to use the revised third tissue component concentration prediction model to process the new output light intensity to obtain a new measured tissue component concentration.

Under the condition that the fifth preset condition is satisfied, the new output light intensity is processed by using the new third tissue component concentration prediction model to obtain a new measured tissue component concentration.

Obtain the current interference parameter value of each interference parameter in the plurality of interference parameters. The plurality of current interference parameter values and the third output light intensity corresponding to the preset wavelength are input into the fourth tissue component concentration prediction model, and the concentration of the measured tissue component is output.

According to an embodiment of the present disclosure, the fourth tissue component concentration prediction model may be generated by obtaining a fifth training sample set, wherein the fifth training sample set includes a plurality of fifth training samples, wherein each fifth training sample Including the fourth real concentration of the measured tissue component and the output light intensity corresponding to the fourth real concentration, obtaining a sixth training sample set, wherein the sixth training sample set includes a plurality of sixth training samples, wherein each sixth training sample set The training sample includes the training interference parameter value of each interference parameter in the plurality of interference parameters and the light intensity value corresponding to each training interference parameter value. According to the sixth training sample set, a tissue component concentration prediction model to be corrected is established, according to the sixth training sample set. A sample set is trained, a correction parameter model is established, and a fourth tissue component concentration prediction model is obtained according to the tissue component concentration prediction model to be corrected and the correction parameter model.

Under the condition that the fourth preset condition is satisfied, the fourth target concentration of the measured tissue component is obtained, the output light intensity corresponding to the fourth target concentration is obtained, and the current interference parameter value of each interference parameter among the plurality of interference parameters is obtained, Modifying the fourth tissue component concentration prediction model based on the fourth target concentration, the plurality of interference parameter values, and the output light intensity corresponding to the fourth target concentration to process the new output using the revised fourth tissue component concentration prediction model The light intensity and the new multiple current interference parameter values are used to obtain new concentrations of the measured tissue components.

Under the condition that the fifth preset condition is satisfied, the new output light intensity and the new multiple current interference parameter values are processed by using the new fourth tissue component concentration prediction model to obtain a new measured tissue component concentration.

According to an embodiment of the present disclosure, each photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of different photosensitive surfaces are the same or different.

According to an embodiment of the present disclosure, each photosensitive surface may be made of a photosensitive material. The ring-shaped photosensitive surface can avoid the problem of azimuth positioning, and can also realize the design of a large area within a small source detection distance range. It should be noted that, in the measurement of living tissue composition, the source detection distance is usually a relatively important physical quantity, so it is very meaningful to realize a larger area design within a smaller source detection distance range.

According to embodiments of the present disclosure, in some cases, the use of a non-annular photosensitive surface has the following beneficial effects.

First, since the measurement results are affected by the measurement area, usually if the photosensitive surface is set in the measurement area that is conducive to measurement, the photosensitive surface is set in the measurement area that is conducive to measurement, compared to the photosensitive surface set in the measurement area that interferes with the measurement. Better measurement results are obtained, so that the photosensitive surface can be positioned in the right position according to the characteristics of the tissue structure. The non-annular photosensitive surface can easily avoid the measurement area that interferes with the measurement, such as the blood vessel or the wound area. Therefore, the use of the non-annular photosensitive surface will have a better effect.

Second, due to the non-uniformity of the tissue, the transmission paths of the same incident light in the tissue may be different, and thus the average optical paths corresponding to the outgoing light at different outgoing positions are different. Taking the measured tissue component as blood glucose as an example, the dermis is usually the main source of the blood glucose signal, so it is required that the outgoing light is mainly transmitted in the dermis layer. Correspondingly, the average optical path corresponding to the outgoing light is There are certain requirements.

Assuming that the annular photosensitive surface of the corresponding size is designed according to the requirements for the average optical path, it can be considered that the average optical path corresponding to the outgoing light received by the different photosensitive positions of the annular photosensitive surface is basically similar and the outgoing light mainly passes through the dermis, The average optical path is within the average optical path range C. In this case, if the skin tissue is homogeneous, the above conclusion is in line with the actual situation. However, because the skin tissue is usually not uniform, the average optical path difference corresponding to the outgoing light received by different photosensitive positions of the same annular photosensitive surface is relatively large. The average optical path lengths are basically similar, all within the average optical path range C, and the average optical path corresponding to the outgoing light received by another part of the photosensitive surface of the ring-shaped photosensitive surface is quite different from the aforementioned, and is not within the average optical path range C. Since the average optical path of the outgoing light is within the average optical path range C, it can be shown that the outgoing light mainly passes through the dermis layer. The ring-shaped photosensitive surface outputs one output light intensity. Therefore, in the case of uneven skin tissue, the signal quality of the output light intensity obtained by using the ring-shaped photosensitive surface is not high, thereby affecting the reliability of the measurement results.

The non-ring photosensitive surface can be set according to the actual situation. Taking the above example as an example, assuming that the average optical length not within the average optical path range C is within the average optical path range D, two non-ring photosensitive surfaces can be used, where, One non-annular photosensitive surface is used to receive the light intensity value of the outgoing light whose average optical path is within the average optical path range C, and the other non-annular photosensitive surface is used to receive the average optical path of the outgoing light within the average optical path range D The light intensity value of the outgoing light inside and the output light intensity of the two non-ring photosensitive surfaces are consistent with the actual situation, which is beneficial to ensure the reliability of the measurement results.

Third, when using the pulse wave-based time difference measurement method to measure tissue components, it is necessary to make full use of the pulse signal, that is, to make the difference between the systolic light intensity and the diastolic light intensity as large as possible. In the above situation, since most of the annular photosensitive surface is not located above the blood vessel, the collection effect of the pulse signal is affected, and therefore, the degree of difference between the light intensity during systole and the light intensity during diastole is reduced. It can be seen that the difference between the systolic light intensity and the diastolic light intensity obtained by using the annular photosensitive surface is smaller than the difference between the systolic and diastolic light intensity obtained by using the non-ring photosensitive surface.

Fourth, due to the influence of tissue inhomogeneity and physiological background changes on the outgoing light, the average optical path of the outgoing light received by different photosensitive surfaces with the same source detection distance from the center of the incident light may be different. Therefore, it can be used. Differential operation is performed on the output light intensities collected by different photosensitive surfaces with the same source-detection distance from the center of the incident light to measure tissue composition. The above non-annular photosensitive surface can be realized, that is, for the same source detection distance, at least two non-annular photosensitive surfaces can be discretely arranged with the center of the incident light as the center, so as to output two output light intensities.

Fifth, the manufacturing process is less difficult and the manufacturing cost is lower.

The fourth aspect will be described below with reference to FIG. 14 . FIG. 14 schematically shows a schematic diagram of a differential measurement according to an embodiment of the present disclosure. As shown in Figure 14, Figure 14 includes four fan ring photosensitive surfaces, namely fan ring photosensitive surface 1, fan ring photosensitive surface 2, fan ring photosensitive surface 3 and fan ring photosensitive surface 4, and the four fan ring photosensitive surfaces are individually In use, each fan ring photosensitive surface has a corresponding output light intensity. The centers of the four fan-ring photosensitive surfaces have the same distance from the center of the incident light, that is, have the same source-detection distance. Due to the non-uniformity of the tissue, the average optical paths corresponding to the outgoing light received by the fan ring photosensitive surface 1 and the fan ring photosensitive surface 2 are different. Therefore, according to the output light intensity collected by the fan ring photosensitive surface 1 and the fan ring photosensitive surface 2 The collected output light intensity is subjected to differential operation to realize differential measurement.

According to an embodiment of the present disclosure, the non-ring-shaped photosensitive surface includes a fan-shaped photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.

According to an embodiment of the present disclosure, the polygonal photosensitive surface includes a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.

According to the embodiments of the present disclosure, the central angle can be designed according to the actual situation, so as to obtain the corresponding photosensitive surface of the fan ring. For example, a fan ring photosensitive surface with a central angle of 90°, a fan ring photosensitive surface with a central angle of 180°, and a fan ring photosensitive surface with a central angle of 45°.

According to an embodiment of the present disclosure, FIG. 15 schematically shows a schematic diagram of a ring-shaped photosensitive surface according to an embodiment of the present disclosure. FIG. 16 schematically shows a schematic diagram of a fan ring photosensitive surface according to an embodiment of the present disclosure. FIG. 17 schematically shows a schematic diagram of a circular photosensitive surface according to an embodiment of the present disclosure. FIG. 18 schematically shows a schematic diagram of a square photosensitive surface according to an embodiment of the present disclosure.

According to an embodiment of the present disclosure, the same type of photosensitive surface includes an annular photosensitive surface or a non-annular photosensitive surface, wherein the same type of photosensitive surface includes one or more photosensitive surfaces, and the same type of photosensitive surface is used to output one output light intensity.

According to an embodiment of the present disclosure, the same type of photosensitive surface may be a ring-shaped photosensitive surface or a non-annular photosensitive surface, that is, the same type of photosensitive surface appears as a ring-shaped photosensitive surface or a non-annular photosensitive surface as a whole. According to the number of photosensitive surfaces included in the same type of photosensitive surface, it can be determined whether the overall shape is formed by a single photosensitive surface or formed by a combination of multiple photosensitive surfaces. The shape of each photosensitive surface in the same type of photosensitive surface may be an annular photosensitive surface or a non-annular photosensitive surface.

According to an embodiment of the present disclosure, the same type of photosensitive surface is an annular photosensitive surface, which may include: in the case that the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent annular photosensitive surface. When the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a ring-shaped photosensitive surface formed by combining the multiple photosensitive surfaces. The same type of photosensitive surface is a non-annular photosensitive surface, which may include: in the case that the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed according to the combination of the multiple photosensitive surfaces.

According to the embodiment of the present disclosure, the plurality of photosensitive surfaces participating in the combination are closely arranged to ensure that there is no gap between adjacent photosensitive surfaces as much as possible. Since the circular photosensitive surface or the square photosensitive surface is more common at present, the manufacturing process is less difficult and the manufacturing cost is lower, while the photosensitive surface of other shapes usually needs to be customized, the manufacturing process is more difficult and the manufacturing cost is higher. Therefore, if limited In terms of production cost, a combination method can be used to combine multiple circular photosensitive surfaces and/or multiple square photosensitive surfaces to form similar photosensitive surfaces of other shapes. Among them, square includes square and rectangle.

In addition, the production cost of the photosensitive surface is also related to the area of the photosensitive surface. Generally, the larger the area of the photosensitive surface, the higher the production cost. If a larger-area photosensitive surface is required, and there are currently multiple smaller-area photosensitive surfaces, in order to reduce the manufacturing cost, multiple smaller-area photosensitive surfaces can be combined to obtain a larger-area photosensitive surface.

According to an embodiment of the present disclosure, in the case where it is determined that the distance between the same type of photosensitive surface and the target site is greater than or equal to the second distance threshold, the same type of photosensitive surface includes a ring photosensitive surface, a fan ring photosensitive surface, a fan-shaped photosensitive surface, a circular photosensitive surface or Square photosensitive surface.

According to the embodiments of the present disclosure, when it is determined that the distance between the same photosensitive surface and the target site is greater than or equal to the second distance threshold, a photosensitive surface with an appropriate shape can be selected according to the jitter of the actual emitted light to minimize the jitter adverse effects on measurements.

The target site may be the site where jitter occurs. Since one of the sources of jitter is pulse beating, and pulse beating is related to blood vessels, the target site can be blood vessels. Generally, the jitter distribution of the outgoing light close to the blood vessel has a certain directionality, while the jitter distribution of the outgoing light far from the blood vessel is relatively uniform and has no directionality.

If the same type of photosensitive surface is far away from the target part (for example, the target blood vessel), it means that the jitter distribution of the outgoing light is relatively uniform. photosensitive surface. That the photosensitive surfaces of the same type are far away from the target portion can be understood as the distance between each photosensitive surface of the same photosensitive surface from the target portion is greater than or equal to the second distance threshold. The distance between each photosensitive surface of the same type of photosensitive surface and the target site is greater than or equal to the second distance threshold value may include that the distance between the edge of the photosensitive surface of the same type of photosensitive surface closest to the target site and the target site is greater than or equal to the second distance threshold value, or, The photosensitive surfaces of the same type are not in contact with the target part, and the distance from the center of the photosensitive surface closest to the target part in the photosensitive surfaces of the same type to the target part is greater than or equal to the second distance threshold.

In the case where the same photosensitive surface is far away from the target part, if the average optical path of the outgoing light received by different photosensitive positions of each photosensitive surface in the same photosensitive surface is less than or equal to the optical path threshold, it can be shown that the jitter of the outgoing light is affected by the light. The influence of the size of the optical path, wherein, the larger the average optical path of the outgoing light, the more obvious the jitter of the outgoing light, and vice versa, the less obvious the jitter of the outgoing light. In this case, the arc length corresponding to the position farther from the center of the incident light can be designed to be longer, so that a ring-shaped photosensitive surface, a fan-shaped photosensitive surface or a fan-shaped photosensitive surface can be selected.

In the case where the same photosensitive surface is far away from the target part, if the average optical path of the outgoing light received by different photosensitive positions of each photosensitive surface in the same photosensitive surface is greater than the optical path threshold, it can indicate the jitter of the outgoing light and the size of the optical path almost irrelevant. In this case, a circular photosensitive surface or a square photosensitive surface can be selected.

According to an embodiment of the present disclosure, in the case where the same type of photosensitive surface is a fan ring photosensitive surface, if the same type of photosensitive surface includes one photosensitive surface, the fan ring photosensitive surface is an independent fan ring photosensitive surface. If the same photosensitive surface includes multiple photosensitive surfaces, the fan ring photosensitive surface is a photosensitive surface formed by combining the multiple photosensitive surfaces. Similarly, for the case where the same type of photosensitive surface includes a ring-shaped photosensitive surface, a circular photosensitive surface, a square photosensitive surface or a fan-shaped photosensitive surface, it can be the same type of photosensitive surface formed independently or the same type of photosensitive surface formed in combination.

It should be noted that, because the current circular photosensitive surface or square photosensitive surface is more common, the production process is less difficult and the production cost is low, while the photosensitive surface of other shapes usually needs to be customized, the production process is more difficult, and the production cost is high. Therefore, if limited by the manufacturing cost, if the distance between the same type of photosensitive surface and the target site is determined to be greater than or equal to the second distance threshold, the same type of photosensitive surface includes a circular photosensitive surface or a square photosensitive surface.

According to the embodiment of the present disclosure, when it is determined that the distance between the same type of photosensitive surface and the target site is less than or equal to the third distance threshold, the shape of the same type of photosensitive surface is determined according to the jitter distribution of the outgoing light.

According to the embodiment of the present disclosure, if the same type of photosensitive surface is close to the target part (for example, the target blood vessel), it can be shown that the jitter distribution of the outgoing light has a certain directionality. In this case, the shapes of the photosensitive surfaces of the same type can be determined according to the jitter distribution of the outgoing light. Alternatively, the shapes of the photosensitive surfaces of the same type and the jitter distribution of the outgoing light are similar figures. Exemplarily, if the jitter distribution of the outgoing light is an elliptical shape, the shape of the same photosensitive surface can be designed to be an elliptical photosensitive surface. Alternatively, if the jitter distribution of the outgoing light is rectangular, the shape of the photosensitive surface of the same type can be designed to be a rectangular photosensitive surface. Alternatively, if the jitter distribution of the outgoing light is rhombic, the shape of the same photosensitive surface can be designed to be a rhombus photosensitive surface.

According to an embodiment of the present disclosure, the jitter distribution of the outgoing light includes a jitter distribution along a first direction and a jitter distribution along the second direction, the first direction and the second direction are perpendicular to each other, and the same photosensitive surfaces are along the first direction. The ratio of the upward length to the length of the same photosensitive surface along the second direction is determined according to the ratio of the jitter amplitude of the outgoing light in the first direction to the jitter amplitude of the outgoing light in the second direction. The upward jitter is the largest.

According to an embodiment of the present disclosure, if the jitter distribution of the outgoing light includes jitter distributions along two mutually perpendicular directions, the jitter distributions in the two mutually perpendicular directions are obtained by decomposing the jitter of the outgoing light into these two mutually perpendicular directions. obtained from the direction of By setting the ratio of the length of the same type of photosensitive surface along the first direction to the length along the second direction, it can make the length of the same type of photosensitive surface along the first direction and the length along the second direction. The ratio is greater than or equal to the ratio of the dither amplitudes of the outgoing light along the first direction and along the second direction.

Exemplarily, if the first direction and the second direction are the Y-axis direction and the X-axis direction in the Cartesian coordinate system, respectively, the ratio of the shaking amplitude along the Y-axis direction of the outgoing light to the shaking amplitude along the X-axis direction can be expressed as: for

The ratio of the length of the same photosensitive surface along the Y-axis direction to the length along the X-axis direction can be expressed as

but

According to an embodiment of the present disclosure, the same type of photosensitive surface includes a rectangular photosensitive surface or an elliptical photosensitive surface, and the ratio of the length to the width of the rectangular photosensitive surface is based on the jitter amplitude of the outgoing light in the first direction and the outgoing light in the second direction. The ratio of the jitter amplitude is determined, and the ratio of the major axis to the minor axis of the elliptical photosensitive surface is determined according to the ratio of the jitter amplitude of the emitted light along the first direction to the jitter amplitude of the emitted light along the second direction.

According to an embodiment of the present disclosure, if the distance between the same photosensitive surface and the target site is less than or equal to the third distance threshold, the shaking distribution of the emitted light is shaken along the first direction and the second direction, and the first direction and the second direction are mutually Vertical, the same photosensitive surface can include a rectangular photosensitive surface or an elliptical photosensitive surface. Wherein, the ratio of the length to the width of the rectangular photosensitive surface is greater than or equal to the ratio of the shaking amplitude of the emitted light along the first direction to the shaking amplitude along the second direction. The ratio of the long axis to the short axis of the elliptical photosensitive surface is greater than or equal to the ratio of the shaking amplitude along the first direction to the shaking amplitude along the second direction of the outgoing light.

According to an embodiment of the present disclosure, each output light intensity is obtained by processing according to the light intensity value of the outgoing light collected by one or more photosensitive surfaces, which may include the following operations.

Combine one or more photosensitive surfaces to produce one output light intensity. Or, in the case where each photosensitive surface of the one or more photosensitive surfaces is used independently, an output light intensity is obtained by calculating the light intensity value of the outgoing light collected by each photosensitive surface.

According to an embodiment of the present disclosure, a photosensitive surface for outputting one output light intensity is referred to as a similar photosensitive surface, and a similar photosensitive surface may include one or more photosensitive surfaces. Wherein, the condition for the combined use of different photosensitive surfaces may be that the average optical length of the outgoing light received by each photosensitive surface is within the range of the average optical length. The average optical path range may be a range consisting of greater than or equal to the first average optical path threshold and less than or equal to the second average optical path threshold. The first average optical path threshold and the second average optical path threshold may be determined according to the optical path average value and the optical path variation amplitude. The average optical path length is an average value calculated from the average optical path lengths of the outgoing light received by each photosensitive surface of the same type of photosensitive surface.

The photosensitive surface is usually used in conjunction with the amplifier circuit corresponding to the photosensitive surface to output a light intensity value. In order to enable the same type of photosensitive surface to output more accurate output light intensity, the product of the photoresponsivity of each photosensitive surface in the same photosensitive surface and the magnification of the amplification circuit used in conjunction with the photosensitive surface needs to be a preset value. When the light responsivity of each photosensitive surface and the magnification of the amplifying circuit used in conjunction with the photosensitive surface are the same preset value, the same type of photosensitive surface can output one output light intensity. If the product of the photoresponsivity of the photosensitive surface and the magnification of the amplifying circuit used in conjunction with the photosensitive surface is not the same preset value, a corresponding method needs to be taken to make the product be the same preset value.

The same type of photosensitive surface can output one output light intensity by means of hardware or software.

The first method is the hardware method. The cathodes of different photosensitive surfaces of the same photosensitive surface can be electrically connected to each other and the anodes of the same photosensitive surfaces can be electrically connected to each other, that is, the electrical connection of common cathode and common anode between different photosensitive surfaces can be realized. In this case, it is equivalent to connecting different photosensitive surfaces in parallel, so that one or more photosensitive surfaces are used in combination to output one output light intensity. It should be noted that it is necessary to ensure that the light responsivity of different photosensitive surfaces is consistent as much as possible, so as to obtain a more accurate output light intensity.

The second method is the software method. The cathodes between different photosensitive surfaces in the same photosensitive surface are not connected to each other and the anodes are not connected to each other, that is, each photosensitive surface is used alone to output a light intensity value. After the light intensity value corresponding to each photosensitive surface is obtained, a corresponding algorithm can be used to perform a weighted summation of the light intensity values of each photosensitive surface in the same photosensitive surface to obtain an output light intensity.

Alternatively, the output light intensity corresponding to the same type of photosensitive surface can be determined by the following formulas (2) and (3).

Among them, I represents the output light intensity corresponding to the same photosensitive surface, I _i represents the light intensity value corresponding to the photosensitive surface i, i∈{1,2,...,N-1,N},N Indicates the number of photosensitive surfaces included in the same type of photosensitive surface, 1≤N≤M, M denotes the total number of photosensitive surfaces, α _i denotes the weighting coefficient corresponding to the photosensitive surface i, H denotes the preset value, β _i denotes the photosensitive surface i The corresponding photoresponsivity, γ _i represents the magnification of the amplifier circuit used in conjunction with the photosensitive surface i.

At least one superimposed light intensity corresponding to the preset wavelength is determined, wherein the superimposed light intensity is obtained by adding a plurality of output light intensities corresponding to the preset wavelength. The concentration of the measured tissue component is determined according to at least one superimposed light intensity corresponding to a preset wavelength.

According to the embodiments of the present disclosure, when determining the concentration of the measured tissue component, the acquired data can be flexibly used according to the actual situation, such as the value of a single output light intensity is small, or the signal-to-noise ratio of the output light intensity is low , to improve the reliability of the measurement results.

Based on the above, the concentration of the measured tissue component is determined according to at least one superimposed light intensity corresponding to a preset wavelength, wherein the superimposed light intensity may be obtained by adding a plurality of output light intensities. The output light intensity is the light intensity of the diffused light (ie the outgoing light).

According to an embodiment of the present disclosure, the preset wavelength is a wavelength sensitive to the measured tissue composition.

According to the embodiment of the present disclosure, in order to improve the reliability of the measurement result, the preset wavelength may be a wavelength sensitive to the measured tissue composition. Exemplarily, the preset wavelength may be 1550 nm or 1609 nm.

According to an embodiment of the present disclosure, the temperature of the measurement region is maintained within a preset temperature range during tissue composition measurement.

According to the embodiments of the present disclosure, since the temperature change of the measurement area will affect the reliability of the measurement result, in order to ensure the reliability of the measurement result as much as possible, the temperature of the measurement area can be controlled to keep at the temperature of the tissue composition measurement process based on the temperature control method. within the preset temperature range.

According to an embodiment of the present disclosure, the photosensitive surface is obtained by disposing a mask on the initial photosensitive surface, and the light transmittance of the mask is less than or equal to a light transmittance threshold.

According to an embodiment of the present disclosure, the shape of the mask plate is determined according to the shape of the jitter distribution of the outgoing light.

According to the embodiments of the present disclosure, since a circular photosensitive surface or a square photosensitive surface is relatively common at present, the manufacturing process is less difficult and the manufacturing cost is lower, while other shapes of the photosensitive surface usually need to be customized, the manufacturing process is more difficult, and the manufacturing cost is relatively low. Therefore, if it is limited by the production cost, the method of setting a mask plate on the initial photosensitive surface can be adopted, wherein the part of the initial photosensitive surface blocked by the mask plate is less than or equal to the light transmittance of the mask plate. The light transmittance threshold is difficult to receive the light intensity value.

Based on the above, the shape and position of the mask plate can be set according to the actual required shape and area, so as to obtain a photosensitive surface with a preset shape and area. Wherein, the actual required shape and area can be determined according to the jitter distribution of the outgoing light.

Exemplarily, FIG. 19 schematically shows a schematic diagram of setting a mask plate on an initial photosensitive surface to obtain a photosensitive surface according to an embodiment of the present disclosure. In Figure 19, the initial photosensitive surface is a square photosensitive surface, and the photosensitive surface is a circular photosensitive surface.

According to the embodiment of the present disclosure, the intensity distribution of the light spot irradiated by the incident light to the measurement area is uniform.

According to the embodiments of the present disclosure, in order to enable the measured object to perform tissue composition measurement under more relaxed requirements, so as to better ensure the reliability of the measurement results, the intensity distribution of the light spot that ensures that the incident light irradiates the measurement area can be used. achieved in a uniform manner. At the same time, the more uniform the intensity distribution of the light spot irradiated by the incident light to the measurement area, the lower the requirement for the reproducibility of the controllable measurement conditions, and the better the effect of using the differential measurement method to suppress the influence of the uncontrollable measurement conditions on the measurement results. Therefore, the reliability of the measurement results can also be better guaranteed. In addition, since the measures to make the intensity distribution of the incident light spot on the measurement area uniform will attenuate the light energy of the incident light to a certain extent, and the tissue composition measurement requires that the light energy of the incident light cannot be too small, it is necessary to try to Under the condition that the intensity distribution of the incident light spot on the measurement area is uniform, the light energy attenuation of the incident light is as small as possible. In addition, if the incident light is realized by means of optical fiber transmission, the distribution of the incident light spot on the measurement area is uniform, and the adverse effect of fiber jitter on the measurement result is also reduced.

According to an embodiment of the present disclosure, the area of the light spot irradiated by the incident light to the measurement region is greater than or equal to the light spot area threshold.

According to the embodiments of the present disclosure, in order to enable the measured object to perform tissue composition measurement under more relaxed requirements, so as to better ensure the reliability of the measurement results, the area of the light spot irradiated by the incident light to the measurement area may be larger than or equal to the spot area threshold. At the same time, within a certain range, the larger the area of the light spot irradiated by the incident light to the measurement area, the lower the requirement for the reproducibility of the controllable measurement conditions, and the effect of using the differential measurement method to suppress the influence of the uncontrollable measurement conditions on the measurement results. The better, and therefore, the better the reliability of the measurement results can be guaranteed. The light spot area threshold can be set according to the actual situation, which is not specifically limited here. In addition, if the incident light is realized by optical fiber transmission, the area of the light spot irradiated by the incident light to the measurement area is greater than or equal to the light spot area threshold, which also reduces the adverse effect of fiber jitter on the measurement results.

It should be noted that, in order to improve the reliability of the measurement results, it is necessary to ensure the following three aspects as much as possible. First, the measurement device used to realize the tissue composition has the ability to sense the change of the expected tissue composition concentration. Second, the influence of uncontrollable measurement conditions on the measurement results is reduced. Third, control the controllable measurement conditions. The technical solutions provided by the embodiments of the present disclosure ensure the above three aspects.

The measurement device for realizing tissue composition has the ability to sense the concentration change of the expected tissue composition, and achieves high stability and efficiency of receiving outgoing light by adopting a large-area photosensitive surface. In order to reduce the influence of uncontrollable measurement conditions on the measurement results, the differential measurement method is used. Aiming at controlling the controllable measurement conditions, it is realized by adopting an effective control method.

20 schematically shows a block diagram of a tissue composition measurement device according to an embodiment of the present disclosure.

As shown in FIG. 20 , the tissue composition measurement device 2000 includes a light source module 2010 , a collection module 2020 and a processing module 2030 .

The light source module 2010 is used to illuminate the measurement area with incident light of a single preset wavelength, wherein each incident light passes through the measurement area and exits from at least one exit position to form at least one exit light, and the incident light of the incident light includes at least one.

Acquisition module 2020, the acquisition module includes M photosensitive surfaces, each photosensitive surface can collect the light intensity value of the outgoing light emitted from the outgoing position within the preset anti-shake range corresponding to the photosensitive surface, and the acquisition module is used to acquire The light intensity values corresponding to each outgoing light collected by the M photosensitive surfaces are obtained, and T output light intensities are obtained, wherein each output light intensity is processed according to the light intensity value of the outgoing light collected by one or more photosensitive surfaces obtained, 1≤T≤M.

The processing module 2030 is configured to determine the concentration of the measured tissue component according to at least one output light intensity corresponding to a preset wavelength.

According to the embodiment of the present disclosure, the total area of the photosensitive surfaces of the same type is determined according to the tissue structure features in the measurement area, wherein the photosensitive surfaces of the same type include one or more photosensitive surfaces, and the photosensitive surfaces of the same type are used to output an output light intensity.

As shown in FIG. 21 , according to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a first determination module 2040 , a second determination module 2050 and a setting module 2060 .

The first determining module 2040 is used to determine the positioning feature. The second determination module 2050 is configured to determine a measurement area according to the positioning feature, where the measurement area is an area that satisfies the reproducibility of the controllable measurement condition. The setting module 2060 is configured to set the measurement probe at a position corresponding to the measurement area, wherein the measurement probe includes M photosensitive surfaces.

According to an embodiment of the present disclosure, the positioning features include a first gesture positioning feature and an area positioning feature.

The second determination module includes a first adjustment unit and a first determination unit.

The first adjustment unit is configured to adjust the current measurement posture of the measured object to a target measurement posture according to the first posture positioning feature, wherein the target measurement posture is a measurement posture that satisfies the reproducibility of the controllable measurement condition. The first determining unit is configured to determine the measurement area according to the area positioning feature when the current measurement posture is the target measurement posture.

As shown in FIG. 22 , according to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a fixing part 2080, and the fixing part 2080 is used to set the measurement probe 2070 at a position corresponding to the measurement area, wherein the fixing part 2080 is connected to the measurement area. Probe 2070 is integral, partially discrete, or fully discrete.

According to an embodiment of the present disclosure, the fixing part and the measuring probe in FIG. 22 may be integrated or separate.

As shown in FIG. 23 , according to an embodiment of the present disclosure, the fixing part 2080 includes a fixing seat 2081 and a first fitting part 2082 .

The first fitting 2082 is used to set the fixing base 2081 at a position corresponding to the measurement area. The fixing base 2081 is used to fix the measuring probe 2070 . According to an embodiment of the present disclosure, the hardness of the first fitting 20822070 includes a first hardness and a second hardness, wherein the first hardness is smaller than the second hardness, and the first hardness is the first hardness that the first fitting 2082 fixes in the process of fixing the fixing seat 2081 Corresponding to the hardness, the second hardness is the hardness corresponding to the first fitting member 2082 after fixing the fixing seat 2081 .

According to the embodiment of the present disclosure, in order for the first fitting member 2082 to play a fixing role on the fixing seat 2081, the first fitting member 2082 needs to be relatively rigid. At the same time, in order to minimize the influence caused when the first fitting member 2082 fixes the fixing seat 2081, the first fitting member 2082 needs to have a certain degree of flexibility. It can be seen that the above-mentioned requirements are imposed on the hardness of the first fitting member 2082 .

In order to solve the above problem, a method of changing the hardness of the first fitting member 2082 may be adopted, that is, the hardness of the first fitting member 2082 includes the first hardness and the second hardness. Wherein, the first hardness represents the hardness corresponding to the process of fixing the fixing seat 2082 by the first fitting 2082, and the second hardness represents the hardness corresponding to the fixing of the fixing seat 2081 by the first fitting 2082, the first hardness is smaller than the second hardness, The above can try to ensure that the first fitting part 2082 can not only play a fixing role, but also can reduce the influence produced when the first fitting part 2082 fixes the fixing seat 2081 as much as possible.

According to an embodiment of the present disclosure, the first fitting 2082 includes a first Velcro or a first elastic band.

Exemplarily, FIG. 24 schematically shows a schematic diagram of a first fitting according to an embodiment of the present disclosure. The first fitting 2082 in FIG. 24 is a Velcro. Since the material of the matte surface of the Velcro is very soft, the influence generated when the first fitting 2082 is fixed to the fixing seat 2081 can be reduced. At this time, the hardness of the first fitting 2082 is the first hardness. At the same time, in order to enable it to play a fixing role, after the first fitting 2082 fixes the fixing seat 2081, the hook surface can be pasted on the rough surface to increase the hardness of the first fitting 2082. At this time, the first fitting The hardness of the piece 2082 is the second hardness.

According to the embodiment of the present disclosure, since the hardness corresponding to the first matching piece 2082 in the process of fixing the fixing seat 2081 is the first hardness, it can reduce the influence produced when the first matching piece 2082 fixes the fixing seat 2081, therefore, it can be Try to ensure that the skin state of the skin in the measurement area satisfies the first preset condition during the process of setting the fixing seat 2081 at the position corresponding to the measurement area through the first fitting 2082 .

According to an embodiment of the present disclosure, the hardness of the first fitting 2082 is greater than or equal to the first hardness threshold and less than or equal to the second hardness threshold.

According to an embodiment of the present disclosure, in order to meet the hardness requirement of the first fitting member 2082 , in addition to the above-mentioned methods, a material whose hardness is greater than or equal to the first hardness threshold and less than or equal to the second hardness threshold can also be used In the same way, the first matching member 2082 can be used to fix the fixing seat 2081 , and the influence of the first matching member 2082 in fixing the fixing seat 2081 can be reduced as much as possible. It should be noted that, the first hardness threshold and the second hardness threshold may be set according to actual conditions, which are not specifically limited herein.

As shown in FIG. 25 , according to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a first magnetic part 2090 , the whole or part of the first fitting 2082 is a metal hinge, and the first magnetic part 2090 is matched with the first fitting 2082 to fix the fixing base 2081.

According to the embodiment of the present disclosure, in order to meet the hardness requirement of the first fitting member 2082, in addition to the above-mentioned method, the first fitting member 2082 may be entirely or partially a metal hinge. It is realized that the first fitting member 2082 can fix the fixing seat 2081, and the influence generated when the first fitting member 2082 fixes the fixing seat 2081 to 2082 is reduced as much as possible.

For the fixed effect, the implementation is as follows. After the first fitting 2082 completes the fixing of the fixing base 2081, the first magnetic part 2090 can be adsorbed to the first fitting 2082, so that the first magnetic part 2090 cooperates with the first fitting 2082 to fix the fixing base 2081. play a fixed role. See Figure 25. FIG. 25 schematically shows a schematic diagram of another first fitting according to an embodiment of the present disclosure. All of the first fittings 2082 in FIG. 25 are metal hinges. After the first matching member 2082 completes the fixing of the fixing base 2081 , the first magnetic portion 2090 can be adsorbed to the first matching member 2082 . The first magnetic part 2090 may be a micro electromagnet.

In addition, since the metal hinge is a ferromagnetic metal, and the metal is easy to absorb heat, the direct contact between the metal hinge and the skin will have a greater impact on the skin temperature. Therefore, in order to avoid the impact of the metal heat absorption on the skin temperature, the metal hinge can be The way the insulation is placed below. Alternatively, the insulation may be fleece.

The reason why the above can be achieved is that, since the metal hinge has better flexibility, the influence produced when the first fitting member 2082 fixes the fixing seat 2081 can be reduced. At the same time, after the first fitting 2082 completes the fixing of the fixing seat 2081, since the first magnetic part 2090 is adsorbed on the first fitting 2082, the cooperation of the two makes the first fitting 2082 more rigid. Therefore, the first fitting 2082 can be achieve a fixed effect.

It should be noted that, since all or part of the first matching member 2082 is a metal hinge, and the metal hinge is more flexible, it can reduce the influence of the first matching member 2082 when the fixing seat 2081 is fixed. Therefore, it can be ensured as much as possible. The skin state of the skin of the skin at the measurement area satisfies the first preset condition during the process of setting the fixing seat 2081 at the position corresponding to the measurement area through the first fitting 2082 .

According to an embodiment of the present disclosure, the surface of the first fitting 2082 is provided with holes.

According to an embodiment of the present disclosure, the measurement probe 2070 is fixed to the fixing base 2081 in at least one of the following manners: the measurement probe 2070 is fixed to the fixing base 2081 by an adhesive tape. The measuring probe 2070 is fixed to the fixing base 2081 by fasteners. The measuring probe 2070 is fixed to the fixing base 2081 by magnetic force. The friction coefficient between the measuring probe 2070 and the fixing base 2081 is greater than or equal to the friction coefficient threshold.

According to the embodiment of the present disclosure, in order to realize that the measurement probe 2070 is fixed to the fixed seat 2081 and ensure that the measurement probe 2070 does not move in the fixed seat 2081, at least one of the following methods can be adopted.

In a first way, the measuring probe 2070 can be fixed to the fixing base 2081 by tape. In the second way, the measuring probe 2070 can be fixed to the fixing base 2081 by a fastener. In the third way, the measuring probe 2070 can be fixed to the fixing base 2081 by magnetic force. In the fourth mode, the friction coefficient between the measuring probe 2070 and the fixing seat 2081 is greater than or equal to the friction coefficient threshold. Alternatively, the material of the fixing base 2081 includes rubber, aluminum or plastic.

According to an embodiment of the present disclosure, the fixing part 2080 includes a second fitting.

The second fitting is used to set the measurement probe 2070 at a position corresponding to the measurement area.

According to an embodiment of the present disclosure, the hardness of the second fitting includes a third hardness and a fourth hardness, wherein the third hardness is smaller than the fourth hardness, and the third hardness corresponds to the process of fixing the measurement probe 2070 by the second fitting Hardness, the fourth hardness is the hardness corresponding to the second fitting member after fixing the measuring probe 2070 .

According to an embodiment of the present disclosure, the second fitting includes a second Velcro or a second elastic band.

According to an embodiment of the present disclosure, the hardness of the second fitting is greater than or equal to the third hardness threshold and less than or equal to the fourth hardness threshold.

According to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a second magnetic part, all or part of the second fitting is a metal hinge, and the second magnetic part cooperates with the second fitting to fix the measurement probe 2070 .

According to an embodiment of the present disclosure, the surface of the second fitting is provided with holes.

According to the embodiment of the present disclosure, for the relevant description of the second fitting member, reference may be made to the description of the first fitting member 2082 above, and details are not repeated here. The difference is that the second fitting is used to fix the measuring probe 2070 .

According to an embodiment of the present disclosure, the area positioning feature is provided on at least one of the measurement probe 2070 , the fixing part 2080 and the measured object.

The first determining unit is used for: acquiring the first projection feature. In the case where it is determined that the regional positioning feature does not match the first projection feature, the position of the measuring probe 2070 and/or the fixing part 2080 is adjusted until the regional positioning feature matches the first projection feature. In the case where it is determined that the region positioning feature matches the first projection feature, the region corresponding to the measurement probe 2070 and/or the fixing portion 2080 is determined as the measurement region.

As shown in FIG. 26 and FIG. 27 , according to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a region positioning part 2100 , and the region positioning part 2100 is arranged on the object to be measured, the measurement probe 2070 , the fixing part 2080 or other objects, The area positioning part 2100 is used for projecting the first projection feature.

According to an embodiment of the present disclosure, in the case where it is determined that the region positioning part 2100 is provided on the measurement probe 2070 , the region positioning feature is not provided on the measurement probe 2070 . When it is determined that the region positioning portion 2100 is provided on the fixing portion 2080 , the region positioning feature is not provided on the fixing portion 2080 .

According to an embodiment of the present disclosure, FIG. 26 schematically shows a schematic diagram of a region positioning part according to an embodiment of the present disclosure. The measuring probe 2070 and the fixing part 2080 are not shown in FIG. 26 , and the area positioning part 2100 is used to project the first projection feature, and the first projection feature is a cross light spot. The regional positioning feature is the cross mark point.

FIG. 27 schematically shows a schematic diagram of another area positioning part according to an embodiment of the present disclosure. In FIG. 27 , the area positioning part 2100 is integrated with the measuring probe 2070 and the fixing part 2080 , and the area positioning feature is set on the back of the hand of the measured object. The area positioning part 2100 is used to project the first projection feature, and the first projection feature is a cross light spot.

According to an embodiment of the present disclosure, the area positioning part 2100 includes a first laser.

According to an embodiment of the present disclosure, the first laser may project a spot of a preset shape to form the first projection feature.

According to an embodiment of the present disclosure, the first determination unit is configured to: acquire the first target image. A first template image is acquired, wherein the first template image includes regional positioning features. When it is determined that the first target image does not match the first template image, adjust the position of the measuring probe 2070 and/or the fixing part 2080 to acquire a new first target image until the new first target image matches the first template Image matching. When it is determined that the first target image matches the first template image, an area corresponding to the measurement probe 2070 and/or the fixing part 2080 is determined as a measurement area.

As shown in FIG. 28 , according to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a first image acquisition part 2110 , and the first image acquisition part 2110 is arranged on the object to be measured, the measurement probe 2070 , the fixing part 2080 or other objects , the first image acquisition part 2110 is used to acquire the first target image.

According to an embodiment of the present disclosure, FIG. 28 schematically shows a schematic diagram of a first image acquisition part according to an embodiment of the present disclosure. In FIG. 28 , the first image acquisition part 2110 is integrated with the measurement probe 2070 and the fixing part 2080 , and the area positioning feature is set on the back of the hand of the measured object. The first image acquisition part 2110 is used for acquiring a first target image. The first image acquisition part 2110 may be an image sensor.

According to an embodiment of the present disclosure, the first determination unit is configured to: acquire a second target image, wherein the second target image includes a region localization feature. If it is determined that the position of the region positioning feature in the second target image is not the first preset position, adjust the position of the measuring probe 2070 and/or the fixing part 2080 to acquire a new second target image until a new second target image is obtained. The position of the regional positioning feature in the target image is the first preset position. In the case that the position of the region positioning feature in the new second target image is determined to be the first preset position, the region corresponding to the measurement probe 2070 and/or the fixing part 2080 is determined as the measurement region.

According to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a second image acquisition part, the second image acquisition part is arranged on the measured object, the measurement probe 2070 , the fixing part 2080 or other objects, and the second image acquisition part is used for A second target image is acquired.

According to an embodiment of the present disclosure, the second image capturing part is the same as or different from the first image capturing part 2110 .

According to an embodiment of the present disclosure, in a case where it is determined that the second image acquisition part is provided on the measurement probe 2070 , the area positioning feature is not provided on the measurement probe 2070 . In the case where it is determined that the second image capturing part is arranged on the fixing part 2080 , the area positioning feature is not arranged on the fixing part 2080 .

According to an embodiment of the present disclosure, the first adjustment unit is configured to: acquire the second projection feature. In the case where it is determined that the first posture locating feature does not match the second projection feature, the current measurement posture is adjusted until the first posture locating feature and the second projection feature match. When it is determined that the first posture positioning feature matches the second projection feature, it is determined that the current measurement posture is the target measurement posture.

As shown in FIG. 29 , according to an embodiment of the present disclosure, the tissue composition measuring device 2000 further includes a first posture positioning part 2120 , and the first posture positioning part 2120 is arranged on the measured object, the measuring probe 2070 , the fixing part 2080 or other objects , the first posture positioning part 2120 is used to project the second projection feature.

According to an embodiment of the present disclosure, in a case where it is determined that the first posture positioning part 2120 is provided on the measurement probe 2070 , the first posture positioning feature is not provided on the measurement probe 2070 . When it is determined that the first posture positioning portion 2120 is provided on the fixing portion 2080 , the first posture positioning feature is not provided on the fixing portion 2080 .

According to an embodiment of the present disclosure, FIG. 29 schematically shows a schematic diagram of a first posture positioning part according to an embodiment of the present disclosure. The measuring probe 2070 and the fixing part 2080 are not shown in FIG. 29 , and the first posture positioning part 2120 is used to project the second projection feature, and the second projection feature is a cross light spot. The first pose localization feature is a cross mark point.

FIG. 30 schematically shows a schematic diagram of another first posture positioning part according to an embodiment of the present disclosure. In FIG. 30 , the first posture positioning part 2120 is integrated with the measuring probe 2070 and the fixing part 2080 , and the first posture positioning feature is set on the back of the hand of the measured object. The first posture positioning part 2120 is used to project the second projection feature, and the second projection feature is a cross light spot.

According to an embodiment of the present disclosure, the first posture positioning part 2120 includes a second laser.

According to an embodiment of the present disclosure, the second laser may project a predetermined shaped light spot to form the second projection feature.

According to an embodiment of the present disclosure, the first adjustment unit is configured to: acquire a third target image. A second template image is acquired, wherein the second template image includes the first gesture location feature. When it is determined that the third target image does not match the second template image, the current measurement posture is adjusted to obtain a new third target image until the new third target image matches the second template image. When it is determined that the new third target image matches the second template image, it is determined that the current measurement posture is the target measurement posture.

As shown in FIG. 31 , according to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a third image acquisition part 2130 , and the third image acquisition part 2130 is disposed on the object to be measured, the measurement probe 2070 , the fixing part 2080 or other objects , and the third image acquisition part 2130 is used to acquire a third target image.

According to an embodiment of the present disclosure, FIG. 31 schematically shows a schematic diagram of a third image acquisition part according to an embodiment of the present disclosure. In FIG. 31 , the third image acquisition part 2130 is integrated with the measurement probe 2070 and the fixing part 2080 , and the first posture positioning feature is set on the back of the hand of the measured object. The third image acquisition part 2130 is used to acquire a third target image. The third image acquisition part 2130 may be an image sensor.

According to an embodiment of the present disclosure, the third image capturing part 2130 , the first image capturing part 2110 and the second image capturing part may be different, partially the same, or all the same.

According to an embodiment of the present disclosure, the first adjustment unit is configured to: acquire a fourth target image, wherein the fourth target image includes the first posture positioning feature. In the case where it is determined that the position of the first posture positioning feature in the fourth target image is not at the second preset position, adjust the current measurement posture to obtain a new fourth target image until the first posture is positioned in the new fourth target image The location of the feature is at the second preset location. When it is determined that the position of the first posture positioning feature in the new fourth target image is at the second preset position, the current measurement posture is determined as the target measurement posture.

According to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a fourth image acquisition part, the fourth image acquisition part is arranged on the measured object, the measurement probe 2070 , the fixing part 2080 or other objects, and the fourth image acquisition part is used for A fourth target image is acquired.

According to an embodiment of the present disclosure, the fourth image capturing part, the third image capturing part 2130, the first image capturing part 2110, and the second image capturing part may be different, partially the same, or all the same.

According to an embodiment of the present disclosure, in a case where it is determined that the fourth image acquisition part is provided on the measurement probe 2070 , the first posture positioning feature is not provided on the measurement probe 2070 . In the case where it is determined that the fourth image capturing part is provided on the fixing part 2080 , the first posture positioning feature is not provided on the fixing part 2080 .

According to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a third determination module and an adjustment module.

The third determining module is configured to determine the second posture positioning feature if the measurement probe 2070 is set at a position corresponding to the measurement area, in the case that the current measurement posture is not the target measurement posture. The adjustment module is configured to adjust the current measurement posture to the target measurement posture according to the second posture positioning feature.

According to an embodiment of the present disclosure, the second posture positioning feature is provided on at least one of the measurement probe 2070 , the fixing portion 2080 , and the measured object.

The adjustment module includes a first acquisition unit, a second adjustment unit and a second determination unit.

The first obtaining unit is used to obtain the third projection feature. The second adjustment unit is configured to adjust the current measurement posture when it is determined that the second posture positioning feature does not match the third projection feature until the second posture positioning feature matches the third projection feature. The second determining unit is configured to determine the current measurement posture as the target measurement posture when it is determined that the second posture positioning feature matches the third projection feature.

According to an embodiment of the present disclosure, the tissue composition measuring device 2000 further includes a second posture positioning part, the second posture positioning part is arranged on the measured object, the measuring probe 2070 , the fixing part 2080 or other objects, and the second posture positioning part is used for Project a third projected feature.

According to an embodiment of the present disclosure, in a case where it is determined that the second posture positioning part is provided on the measuring probe 2070 , the second posture positioning feature is not provided on the measuring probe 2070 and the fixing part 2080 . In the case where it is determined that the second posture positioning part is provided on the fixing part 2080 , the second posture positioning feature is not provided on the measuring probe 2070 and the fixing part 2080 .

According to an embodiment of the present disclosure, the second posture positioning part is the same as or different from the first posture positioning part 2120 .

According to an embodiment of the present disclosure, the second posture positioning portion includes a third laser.

According to an embodiment of the present disclosure, the third laser may project a predetermined shaped light spot to form the third projection feature.

According to an embodiment of the present disclosure, the adjustment module includes a second acquisition unit, a third acquisition unit, a third adjustment unit, and a third determination unit.

The second acquiring unit is configured to acquire the fifth target image. A third acquiring unit, configured to acquire a third template image, wherein the third template image includes the second posture positioning feature. A third adjustment unit, configured to adjust the current measurement posture to obtain a new fifth target image when it is determined that the fifth target image does not match the third template image, until the new fifth target image and the third template image match. The third determination unit is configured to determine the current measurement posture as the target measurement posture when it is determined that the new fifth target image matches the third template image.

According to an embodiment of the present disclosure, the tissue composition measurement device further includes a fifth image acquisition part, the fifth image acquisition part is arranged on the measured object, the measurement probe 2070 , the fixing part 2080 or other objects, and the fifth image acquisition part is used for acquiring Fifth target image. ,

According to an embodiment of the present disclosure, the adjustment module includes a fourth acquisition unit, a fourth adjustment unit, and a fourth determination unit.

The fourth acquisition unit is configured to acquire a sixth target image, wherein the sixth target image includes the second posture positioning feature. The fourth adjustment unit is configured to adjust the current measurement posture to obtain a new sixth target image when it is determined that the position of the second posture positioning feature in the sixth target image is not at the third preset position, until the new sixth The position of the second gesture positioning feature in the target image is at a third preset position. The fourth determining unit is configured to determine the current measurement posture as the target measurement posture when it is determined that the position of the second posture positioning feature in the new sixth target image is at the third preset position.

According to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a sixth image acquisition part, the sixth image acquisition part is arranged on the measured object, the measurement probe 2070 , the fixing part 2080 or other objects, and the sixth image acquisition part is used for A sixth target image is acquired.

According to an embodiment of the present disclosure, in a case where it is determined that the sixth image acquisition part is provided on the measurement probe 2070 , the second posture positioning feature is not provided on the measurement probe 2070 and the fixing part 2080 . In the case where it is determined that the sixth image capturing part is provided on the fixing part 2080 , the second posture positioning feature is not provided on the measuring probe 2070 and the fixing part 2080 .

According to an embodiment of the present disclosure, the sixth image acquisition part, the fifth image acquisition part, the fourth image acquisition part, the third image acquisition part 2130, the first image acquisition part 2110, and the second image acquisition part may be different, partially the same, or All the same.

According to an embodiment of the present disclosure, when an optical method is used to locate the measurement area and the measurement posture, the area locating part 2100 , the first posture locating part 2120 and the second posture locating part may be all the same, partially the same, or all different The said part is the same means that two of the above three structures are the same. If the three structures are all the same, it can be stated that the same structure can be used to generate the first projected feature, the second projected feature and the third projected feature. The above manner can simplify the complexity of the positioning structure.

When the image matching method is used to locate the measurement area and the measurement posture, the first image acquisition part 2110, the third image acquisition part 2130 and the fifth image acquisition part may be all the same, partially the same or all different, The said part is the same means that two of the above three structures are the same. If the three structures are all the same, it can be stated that the same structure can be used to generate the first target image, the third target image and the fifth target image. The above manner can simplify the complexity of the positioning structure.

When the imaging method is used to locate the measurement area and the measurement posture, the second image acquisition part, the fourth image acquisition part and the sixth image acquisition part may be all the same, partially the same or all different, and the parts are the same It means that two of the above three structures are the same. If the three structures are all the same, it can be stated that the same structure can be used to generate the second target image, the fourth target image and the sixth target image. The above manner can simplify the complexity of the positioning structure.

The optical method is used as an example for description below.

The area positioning unit 2100, the first posture positioning unit 2120, and the second posture positioning unit have the same structure. The second pose location feature is identical to the region location feature and is partially identical to the first pose location feature. The measurement area is the extended side of the forearm.

FIG. 32 schematically shows a schematic diagram of a measurement posture and measurement area positioning according to an embodiment of the present disclosure. In FIG. 32 , the area positioning part 2100 , the first attitude positioning part 2120 and the second attitude positioning part all include laser 1 and laser 2 . The laser 1 and the laser 2 are provided in the measurement probe 2070 .

When the first measurement posture positioning is performed, the measurement probe 2070 is set on the base. Before the first measurement posture positioning is completed, the position of the measurement probe 2070 is fixed. According to the first posture positioning feature and the second projection feature, adjust the current measurement posture until the first posture positioning feature and the second projection feature match, and in the case of matching, the first measurement posture positioning is completed.

When positioning the measurement area, the measurement probe 2070 is set on the object to be measured, and the position of the measurement probe 2070 is adjusted according to the area location feature and the first projection feature until the area location feature matches the first projection feature. Next, it explains that the positioning of the measurement area is completed.

After the measurement probe 2070 is set on the object to be measured, if the current measurement posture is not the target posture, before the measurement, it is necessary to perform the positioning of the measurement posture again. According to the second posture positioning feature and the third projection feature, adjust the current measurement posture until the second posture positioning feature and the third projection feature match.

The region positioning unit 2100, the first posture positioning unit 2120, and the second posture positioning unit have the same configuration. The region location feature is exactly the same as the second gesture location feature, and is partially the same as the first gesture location feature. The measurement area is the extended side of the forearm.

FIG. 33 schematically shows another schematic diagram of measurement posture and measurement area positioning according to an embodiment of the present disclosure. In FIG. 33 , the area positioning part 2100 and the second posture positioning part both include the laser 3 and the laser 4 . The first posture positioning unit 2120 includes the laser 5 and the laser 6 . The laser 3 and the laser 4 are provided in the measurement probe 2070 . The laser 5 and the laser 6 are provided on the base.

According to an embodiment of the present disclosure, the tissue composition measurement device further includes a prompting module.

The prompting module is used to generate prompting information, wherein the prompting information is used to prompt that the measurement posture positioning and/or the measurement area positioning is completed, and the form of the prompting information includes at least one of image, voice or vibration.

According to an embodiment of the present disclosure, when it is determined that the fixing base 2081 is provided at a position corresponding to the measurement area and the measuring probe 2070 is not provided on the fixing part 2080 , the measuring probe 2070 is set on the fixing base 2081 .

When it is determined that the fixing base 2081 is not set at the position corresponding to the measurement area, the fixing base 2081 is set at the position corresponding to the measurement area through the first fitting 2082 , and the measurement probe 2070 is set on the fixing base 2081 .

According to an embodiment of the present disclosure, when it is determined that the measurement probe 2070 is not arranged at a position corresponding to the measurement area, the measurement probe 2070 is arranged at a position corresponding to the measurement area through the second fitting.

According to an embodiment of the present disclosure, the processing module 2030 is configured to determine the first output light intensity and the second output light intensity from at least two output light intensities corresponding to preset wavelengths. The concentration of the measured tissue component is determined according to the first output light intensity and the second output light intensity corresponding to the preset wavelength.

Differential processing is performed on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal, which may include the following operations. A differential circuit is used to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, performing differential processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal may include the following operations. A differential algorithm is used to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, using a differential algorithm to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal may include the following operations. A direct differential operation is performed on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, using a differential algorithm to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal may include the following operations. Logarithmic processing is performed on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain the first logarithmic light intensity and the second logarithmic light intensity. Perform a direct differential operation on the first logarithmic light intensity and the second logarithmic light intensity corresponding to the preset wavelength to obtain a differential signal.

According to an embodiment of the present disclosure, the tissue composition measurement device 2000 is also used for:

Acquiring a first training sample set, wherein the first training sample set includes a plurality of first training samples, wherein each first training sample includes a first true concentration of the measured tissue component and a differential signal corresponding to the first true concentration . According to the first training sample set, a first tissue component concentration prediction model is established.

According to an embodiment of the present disclosure, the tissue composition measurement device is further used for:

Obtain a second target concentration of the measured tissue component. A differential signal corresponding to the second target concentration is acquired. Obtain the current interference parameter value of each interference parameter in the plurality of interference parameters. The second tissue component concentration prediction model is modified according to the second target concentration, the plurality of interference parameter values, and the differential signal corresponding to the second target concentration.

According to an embodiment of the present disclosure, one or more photosensitive surfaces of the same type corresponding to the preset wavelengths exist in the M photosensitive surfaces, wherein the same photosensitive surfaces are used to collect the first output light intensity and the corresponding preset wavelengths at different times. /or the second output light intensity, the first output light intensity and the second output light intensity corresponding to the preset wavelength are the output light intensity in the same pulsation period, wherein the first output light intensity is the systolic light intensity, the second output light intensity The output light intensity is the diastolic light intensity, and the same photosensitive surface includes one or more photosensitive surfaces. The processing module 2030 is configured to determine the concentration of the measured tissue component according to the first output light intensity and the second output light intensity corresponding to the preset wavelength.

According to an embodiment of the present disclosure, among the M photosensitive surfaces, there are a first photosensitive surface of the same type and a second photosensitive surface of the same type corresponding to a preset wavelength, wherein the first photosensitive surface of the same type is used to collect the first output corresponding to the preset wavelength Light intensity, the second same type of photosensitive surface is used to collect the second output light intensity corresponding to the preset wavelength, the first same type of photosensitive surface includes one or more photosensitive surfaces, and the second same type of photosensitive surface includes one or more photosensitive surfaces. The processing module 2030 is configured to determine the concentration of the measured tissue component according to the first output light intensity and the second output light intensity corresponding to the preset wavelength.

According to the embodiment of the present disclosure, the M photosensitive surfaces have the same type of photosensitive surface corresponding to the preset wavelength, wherein the same type of photosensitive surface is used to collect the third output light intensity corresponding to the preset wavelength, and the same type of photosensitive surface includes one or more photosensitive surface. The processing module 2030 is configured to determine the concentration of the measured tissue component according to the third output light intensity corresponding to the preset wavelength.

According to the embodiment of the present disclosure, the difference between the average optical length of the outgoing light received by different photosensitive positions of each photosensitive surface of the same type of photosensitive surface and the optimal optical length corresponding to the preset wavelength belongs to the second optical path difference range.

According to an embodiment of the present disclosure, the same type of photosensitive surface is an annular photosensitive surface, including:

In the case where the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent annular photosensitive surface. In the case where the same type of photosensitive surface includes multiple photosensitive surfaces, the same type of photosensitive surface is a ring-shaped photosensitive surface formed by combining the multiple photosensitive surfaces. The same type of photosensitive surface is a non-annular photosensitive surface, including: in the case that the same type of photosensitive surface includes one photosensitive surface, the same type of photosensitive surface is an independent non-annular photosensitive surface. In the case where the same type of photosensitive surface includes a plurality of photosensitive surfaces, the same type of photosensitive surface is a non-annular photosensitive surface formed according to the combination of the multiple photosensitive surfaces.

According to an embodiment of the present disclosure, the anodes of different photosensitive surfaces among the M photosensitive surfaces are not electrically connected to each other, the anodes of some of the photosensitive surfaces are electrically connected, or the anodes of all the photosensitive surfaces are electrically connected.

According to an embodiment of the present disclosure, each of the M photosensitive surfaces may be used independently, and in this case, anodes of different photosensitive surfaces of the M photosensitive surfaces are not electrically connected.

Some of the M photosensitive surfaces may be used in combination, and in this case, the anodes of the different photosensitive surfaces used in combination are electrically connected.

All of the M photosensitive surfaces may be used in combination, in which case the anodes of the different photosensitive surfaces used in combination are electrically connected.

According to an embodiment of the present disclosure, FIG. 34 schematically shows a schematic diagram of an anode electrical connection of different photosensitive surfaces according to an embodiment of the present disclosure. As shown in FIG. 34, the anodes of all the photosensitive surfaces were electrically connected.

According to the embodiments of the present disclosure, different parts of the same photosensitive surface are on the same plane or different planes.

According to an embodiment of the present disclosure, the photosensitive surface may be a flat photosensitive surface or a three-dimensional photosensitive surface, wherein if different parts of the photosensitive surface are on the same plane, the photosensitive surface is a flat photosensitive surface. If there are different parts of the photosensitive surface on different planes, the photosensitive surface is a three-dimensional photosensitive surface, and the specific use of a flat photosensitive surface or a three-dimensional photosensitive surface can be set according to the actual situation, which is not specifically limited here.

Alternatively, for contact measurement, in order to improve the reliability of the measurement result, it is necessary to make the target surface of the photosensitive surface and the skin surface of the measurement area in a good fit state as much as possible. Among them, the target surface of the photosensitive surface refers to the surface close to the measurement area. Since the flatness of the skin surface in the measurement area may not be high, if a flat photosensitive surface is used, it may be difficult to achieve a good fit between the target surface of the photosensitive surface and the skin surface of the measurement area, while the stereo photosensitive surface is There are photosensitive surfaces with different parts in different planes. Therefore, a three-dimensional photosensitive surface can be used, and a specific stereoscopic photosensitive surface can be set according to the organizational structure characteristics of the measurement area.

35 schematically shows a schematic diagram of a stereoscopic photosensitive surface in the form of a glove according to an embodiment of the present disclosure. FIG. 36 schematically shows a schematic diagram of another stereoscopic photosensitive surface in the form of a glove according to an embodiment of the present disclosure.

FIG. 37 schematically shows a schematic diagram of a three-dimensional photosensitive surface in the form of a wristband according to an embodiment of the present disclosure. FIG. 38 schematically shows a schematic diagram of a stereoscopic photosensitive surface in the form of another wristband according to an embodiment of the present disclosure. In FIG. 38, h1 and h2 represent the distances of different parts of the photosensitive surface from the preset plane.

FIG. 39 schematically shows a schematic diagram of a stereoscopic photosensitive surface for arm measurement according to an embodiment of the present disclosure. In FIG. 39 , the distances of different parts of the photosensitive surface from the preset plane can be set according to the structural characteristics of the arm.

According to an embodiment of the present disclosure, the photosensitive surface sets are on the same plane or different planes, wherein the photosensitive surface set includes a plurality of photosensitive surfaces.

According to an embodiment of the present disclosure, each photosensitive surface included in the set of photosensitive surfaces may be a planar photosensitive surface or a three-dimensional photosensitive surface. If the photosensitive surface set includes multiple plane photosensitive surfaces, the photosensitive surface form presented by the photosensitive surface set can be realized by setting some or all of the plane photosensitive surfaces on different planes. It is a three-dimensional photosensitive surface.

It should be noted that, according to the three-dimensional photosensitive surface formed by a plurality of planar photosensitive surfaces, the above-mentioned effects for the contact measurement can also be achieved, which will not be repeated here.

According to an embodiment of the present disclosure, the tissue composition measurement device further includes a temperature control module configured to control the temperature of the measurement region to remain within a preset temperature range during the tissue composition measurement process.

According to an embodiment of the present disclosure, the tissue composition measurement device further includes a mask, which is disposed on the initial photosensitive surface, wherein the light transmittance of the mask is less than or equal to a light transmittance threshold. The mask plate is used to obtain the photosensitive surface after setting the mask plate on the initial photosensitive surface.

As shown in FIG. 40 , according to an embodiment of the present disclosure, the measurement probe 2070 is provided with a first sleeve 2140 . The first end face of the first sleeve extends beyond the target surface of the measurement probe 2070, wherein the first end face represents the end face close to the measurement area, and the target surface of the measurement probe 2070 refers to the surface close to the measurement area.

According to an embodiment of the present disclosure, in order to shield the interference light, the first sleeve 2140 may be provided on the measurement probe 2070 so that the end face of the first sleeve 2140 close to the measurement area exceeds the target surface of the measurement probe 2070 . Interfering light may include surface reflected light and/or diffracted light.

According to an embodiment of the present disclosure, the second end face and/or the inner area of the first sleeve 2140 are provided with scattering objects, wherein the first end face and the second end face are opposite end faces, and the inner area includes a partial inner area or the entire area inside.

According to an embodiment of the present disclosure, in order to make the intensity distribution of the light spot irradiated by the incident light to the measurement area uniform, a manner of disposing scattering objects on the corresponding part of the first sleeve 2140 may be adopted. The scatterer can include sulfated paper, silica gel, or a target mixture, wherein the target mixture can include a mixture of polydimethylsiloxane and titanium dioxide particles.

As shown in FIG. 41 , according to an embodiment of the present disclosure, the tissue composition measurement device 2000 further includes a second sleeve 2150 , and the second sleeve 2150 is disposed outside the target area of the first sleeve 2140 , wherein the target area represents The first sleeve 2140 extends beyond part or all of the target surface of the measurement probe 2070 .

According to the embodiment of the present disclosure, in order to make the light spot irradiated by the incident light to the measurement area as large as possible, a manner of disposing the second sleeve 2150 outside the target area of the first sleeve 2140 may be adopted.

According to an embodiment of the present disclosure, the second sleeve 2150 is provided with a diffuser.

According to the embodiment of the present disclosure, if the second sleeve 2150 is provided, in order to make the intensity distribution of the light spot irradiated by the incident light to the measurement area uniform, a way of disposing scatterers in the corresponding part of the second sleeve 2150 may be adopted.

According to an embodiment of the present disclosure, the inner diameter of the first sleeve 2140 is greater than or equal to the inner diameter threshold.

According to an embodiment of the present disclosure, the opening of the first end surface of the first sleeve 2140 is greater than or equal to the opening of the second end surface of the first sleeve 2140 .

According to an embodiment of the present disclosure, in order to make the incident light irradiated to the measurement area as large as possible, the inner diameter of the first sleeve 2140 may be greater than or equal to the inner diameter threshold, and/or the first end face of the first sleeve 2140 may be used. The opening of the first sleeve 2140 is greater than or equal to the opening of the second end surface of the first sleeve 2140, that is, the opening of the end surface of the first sleeve 2140 close to the measurement area is greater than or equal to the opening of the first sleeve 2140 away from the measurement area. End openings.

As shown in FIGS. 43 to 44 , according to an embodiment of the present disclosure, a refractive index matcher is filled between the photosensitive surface and the measurement area.

According to the embodiments of the present disclosure, the skin surface in the measurement area is unstable due to the jitter, which in turn causes the exit angle of the outgoing light to change, which affects the reliability of the measurement results. The refractive index matching material is filled between the photosensitive surface and the measurement area to improve the stability and efficiency of the photosensitive surface receiving outgoing light.

Illustratively, the jitter caused by pulse beating is taken as an example for description. Pulse beat can be reflected by the state of blood vessels. FIG. 42 schematically shows a schematic diagram of a photosensitive surface receiving outgoing light without filling with a refractive index matcher according to an embodiment of the present disclosure. In FIG. 42 , the blood vessel state 1 represents the vasoconstriction state, the blood vessel state 2 represents the vasodilation state, the skin state 1 represents the skin state corresponding to the blood vessel state 1 , and the skin state 2 represents the skin state corresponding to the blood vessel state 2 . It can be seen from Figure 42 that jitter will cause instability of the skin surface in the measurement area, which in turn will change the exit angle of the exiting light.

FIG. 43 schematically shows a schematic diagram of a photosensitive surface receiving outgoing light under the condition of filling with a refractive index matcher according to an embodiment of the present disclosure.

FIG. 44 schematically shows another schematic diagram of the photosensitive surface receiving the outgoing light under the condition of filling with an index matching material according to an embodiment of the present disclosure.

It can be seen from Figure 43 and Figure 44 that filling the refractive index matching material between the photosensitive surface and the measurement area can improve the stability and efficiency of the photosensitive surface receiving outgoing light.

According to an embodiment of the present disclosure, the included angle between each part of the photosensitive surface and the direction of the corresponding incident light is greater than or equal to 0° and less than or equal to 360°.

According to the embodiment of the present disclosure, the included angle between each part of the photosensitive surface and the direction of the corresponding incident light is greater than or equal to 0° and less than or equal to 360°, so as to realize the diffusion measurement. According to the embodiments of the present disclosure, a suitable location of the photosensitive surface can be determined according to the wavelength characteristic and/or the measurement area characteristic, wherein the wavelength characteristic may include the penetration depth of the wavelength, and the measurement area characteristic may include the thickness of the measurement area. Alternatively, it is generally possible to set the included angle between each part of the photosensitive surface and the direction of the corresponding incident light to form a preset angle.

Exemplarily, if the penetration depth of the wavelength is relatively deep and/or the thickness of the measurement area is relatively thin, the position of the photosensitive surface and the incident position of the corresponding incident light may be located on opposite sides of the measurement area. If the penetration depth of the wavelength is shallow and/or the thickness of the measurement area is thick, the position of the photosensitive surface can be set to be on the same side of the measurement area as the incident position of the corresponding incident light.

Exemplarily, FIG. 45 schematically shows a schematic diagram of a diffusion measurement according to an embodiment of the present disclosure. In Figure 45, the angle between the photosensitive surface C and the incident light is 90°, the position of the photosensitive surface D and the position of the incident light are located on the same side of the measurement area, and the position of the photosensitive surface E and the position of the incident light are located on the different side of the measurement area. side.

Any of the modules, units, or at least part of the functions of any of the modules according to the embodiments of the present disclosure may be implemented in one module. Any one or more of the modules and units according to the embodiments of the present disclosure may be divided into multiple modules for implementation. Any one or more of the modules and units according to the embodiments of the present disclosure may be implemented at least partially as hardware circuits, such as Field Programmable Gate Arrays (FPGA), Programmable Logic Arrays (Programmable Logic Arrays, PLA), system-on-chip, system-on-substrate, system-on-package, Application Specific Integrated Circuit (ASIC), or any other reasonable means of hardware or firmware that can integrate or package a circuit, Or it can be implemented in any one of the three implementation manners of software, hardware and firmware, or in an appropriate combination of any of them. Alternatively, one or more of the modules and units according to the embodiments of the present disclosure may be implemented at least in part as computer program modules, which, when executed, may perform corresponding functions.

For example, any number of acquisition modules and processing modules may be combined into one module/unit for implementation, or any one of the modules/units may be split into multiple modules/units. Alternatively, at least part of the functionality of one or more of these modules/units may be combined with at least part of the functionality of other modules/units and implemented in one module/unit. According to embodiments of the present disclosure, at least one of the acquisition module and the processing module may be implemented at least in part as a hardware circuit, such as a field programmable gate array (FPGA), a programmable logic array (PLA), a system on a chip, a A system, a system on a package, an application specific integrated circuit (ASIC), or any other reasonable means of integrating or packaging a circuit can be implemented in hardware or firmware, or in any one of software, hardware, and firmware implementations or any appropriate combination of any of them. Alternatively, at least one of the acquisition module and the processing module may be implemented, at least in part, as a computer program module that, when executed, may perform corresponding functions.

It should be noted that the tissue composition measurement device in the embodiment of the present disclosure corresponds to the tissue composition measurement method part in the embodiment of the present disclosure, and the description of the tissue composition measurement device part refers to the tissue composition measurement method part, which is not described here. Repeat.

FIG. 46 schematically shows a schematic diagram of a wearable device according to an embodiment of the present disclosure. The wearable device 4600 shown in FIG. 46 is only an example, and should not impose any limitation on the functions and scope of use of the embodiments of the present disclosure.

As shown in FIG. 46 , the wearable device 4600 includes the tissue composition measurement device 2000 .

According to the technical solutions of the embodiments of the present disclosure, a single preset wavelength is used in combination with a photosensitive surface with the above characteristics to measure tissue components, and the real measured tissue component signals are directly obtained. Using a single preset wavelength for tissue composition measurement reduces the volume and structural complexity of the light source module, thereby reducing the volume and structural complexity of devices and equipment, facilitating portable measurement, reducing the capacity requirements for power modules, and reducing cost of production. In addition, the amount of data processing is also reduced.

As shown in FIG. 47 , according to an embodiment of the present disclosure, the wearable device 4600 further includes a buckle portion 4610 and a body 4620 . The buckle portion 4610 and the main body 4620 are used to cooperate to realize the fixation of the tissue composition measuring device 2000 .

According to an embodiment of the present disclosure, FIG. 47 schematically shows a schematic diagram of an assembling process of a wearable device according to an embodiment of the present disclosure.

According to an embodiment of the present disclosure, the quality of the wearable device 4600 is less than or equal to a quality threshold, so that the movement law of the wearable device 4600 is consistent with the skin shaking law at the measurement area.

According to the embodiments of the present disclosure, in order to improve the reliability of the measurement results, the weight of the wearable device 4600 can be made lighter, so that when the wearable device 4600 is set at a position corresponding to the measurement area, the wearable device 4600 can follow The skin shaking at the measurement area, that is, the movement law of the wearable device 4600 can be consistent with the skin shaking law at the measurement area, so that the average optical path length of the outgoing light received by the measurement probe 2070 is kept at a predetermined value during the skin shaking process. within the optical path range. The reason why the average optical path length of the outgoing light received by the measurement probe 2070 can be maintained within the preset optical path range during the skin shaking process at the measurement area is that if the wearable device 4600 can follow the skin shaking at the measurement area, Then, the relative position of the measurement probe 2070 on the measurement area can be kept unchanged or basically unchanged, so that the measurement probe 2070 can receive the outgoing light emitted from the fixed outgoing position. The relative position of the measurement area remains the same or remains substantially unchanged at the exit position. At the same time, during the skin shaking process at the measurement area, the relative position of the incident position of the incident light on the measurement area can remain unchanged or substantially unchanged. Under the circumstance, it can be ensured that the average optical path of the outgoing light remains unchanged as much as possible.

Exemplarily, FIG. 48 schematically illustrates a method according to an embodiment of the present disclosure, under the condition that the wearable device is consistent with the skin shaking law, the average optical path length of the outgoing light received by the measuring probe is kept at the same value during the skin shaking process. Schematic representation of preset optical path ranges. During the skin shaking process, the measurement probe 2070 (not shown in FIG. 48 ) can stably receive the outgoing light emitted from the outgoing position B in the measurement area after the incident light is incident from the incident position A in the measurement area. The movement range of the skin is represented by ζ ₁ , and the movement range of the measuring probe 2070 is represented by ζ ₂ , ζ ₁ −ζ ₂ .

According to an embodiment of the present disclosure, the wearable device 4600 makes the movement amplitude of the skin at the measurement area less than or equal to the movement amplitude threshold.

According to the embodiments of the present disclosure, in order to improve the reliability of the measurement result, the quality of the wearable device 4600 can be made larger, and when the wearable device 4600 is set at a position corresponding to the measurement area, the skin at the measurement area can be pressed against the skin Shaking, that is, the movement amplitude of the skin at the measurement area is less than or equal to the movement amplitude threshold, so that the average optical length of the outgoing light received by the measurement probe 2070 is kept within the preset optical length range during the skin shaking process. The reason why the average optical path length of the outgoing light received by the measurement probe 2070 can be kept within the preset optical path range during the skin shaking process at the measurement area is that if the wearable device 4600 can suppress the skin shaking at the measurement area , the relative position of the measurement probe 2070 on the measurement area can be kept unchanged or substantially unchanged as much as possible, so that the measurement probe 2070 can receive the outgoing light emitted from the fixed outgoing position. At the same time, during the skin shaking process at the measurement area, the relative position of the incident position of the incident light on the measurement area can remain unchanged or substantially unchanged. Under the circumstance, it can be ensured that the average optical path of the outgoing light remains unchanged as much as possible.

Exemplarily, FIG. 49 schematically shows the average light of the outgoing light received by the measurement probe under the condition that the wearable device makes the movement amplitude of the skin at the measurement area less than or equal to the movement amplitude threshold according to an embodiment of the present disclosure. Schematic illustration of how the optical path stays within the preset optical path range during skin shaking. The movement amplitude of the skin at the measurement area in Figure 49 is close to zero.

According to the embodiments of the present disclosure, for the specific description of the tissue component measurement device, reference may be made to the corresponding part above, and details are not repeated here. In addition, the tissue composition measurement device includes a processor that can be executed according to a program stored in a read-only memory (Read-Only Memory, ROM) or a program loaded from a storage portion into a random access memory (RAM) Various appropriate actions and handling. A processor may include, for example, a general-purpose microprocessor (eg, a CPU), an instruction set processor and/or a related chipset, and/or a special-purpose microprocessor (eg, an application specific integrated circuit (ASIC)), among others. Processing may also include on-board memory for caching purposes. The processor may comprise a single processing unit or multiple processing units for performing different actions of the method flow according to the embodiments of the present disclosure.

In the RAM, various programs and data necessary for the operation of the tissue composition measurement device are stored. The processor, ROM, and RAM are connected to each other through a bus. The processor performs various operations of the method flow according to the embodiments of the present disclosure by executing programs in the ROM and/or RAM. Note that the program may also be stored in one or more memories other than ROM and RAM. Processes may also perform various operations of method flows according to embodiments of the present disclosure by executing programs stored in the one or more memories.

According to an embodiment of the present disclosure, the wearable device may further include an input/output (I/O) interface, which is also connected to the bus. The wearable device may also include one or more of the following components connected to the I/O interface: an input portion including a keyboard, mouse, etc.; including components such as a cathode ray tube (CRT), a liquid crystal display (LCD) etc., and an output portion of a speaker, etc.; a storage portion including a hard disk, etc.; and a communication portion including a network interface card such as a LAN card, a modem, and the like. The communication section performs communication processing via a network such as the Internet. Drives are also connected to the I/O interface as required. Removable media, such as magnetic disks, optical disks, magneto-optical disks, semiconductor memories, etc., are mounted on the drive as needed, so that the computer program read therefrom is installed into the storage section as needed.

The present disclosure also provides a computer-readable storage medium. The computer-readable storage medium may be included in the device/apparatus/system described in the above embodiments; it may also exist alone without being assembled into the device/system. device/system. The above-mentioned computer-readable storage medium carries one or more programs, and when the above-mentioned one or more programs are executed, implement the method according to the embodiment of the present disclosure.

According to an embodiment of the present disclosure, the computer-readable storage medium may be a non-volatile computer-readable storage medium. Examples may include, but are not limited to, portable computer disks, hard disks, random access memory (RAM), read only memory (ROM), erasable programmable read only memory (EPROM) or flash memory), portable compact Disk read-only memory (Computer Disc Read-Only Memory, CD-ROM), optical storage device, magnetic storage device, or any suitable combination of the above. In this disclosure, a computer-readable storage medium may be any tangible medium that contains or stores a program that can be used by or in conjunction with an instruction execution system, apparatus, or device.

For example, according to embodiments of the present disclosure, a computer-readable storage medium may include one or more memories other than ROM and/or RAM and/or ROM and RAM described above.

Embodiments of the present disclosure also include a computer program product, which includes a computer program, and the computer program includes program codes for executing the methods provided by the embodiments of the present disclosure.

When the computer program is executed by the processor, the above-described functions defined in the system/apparatus of the embodiments of the present disclosure are performed. According to embodiments of the present disclosure, the systems, apparatuses, modules, units, etc. described above may be implemented by computer program modules.

In one embodiment, the computer program may rely on a tangible storage medium such as an optical storage device, a magnetic storage device, or the like. In another embodiment, the computer program may also be transmitted, distributed in the form of a signal over a network medium, and downloaded and installed through the communication portion, and/or installed from a removable medium. The program code embodied by the computer program may be transmitted using any suitable network medium, including but not limited to: wireless, wired, etc., or any suitable combination of the foregoing.

According to the embodiments of the present disclosure, the program code for executing the computer program provided by the embodiments of the present disclosure may be written in any combination of one or more programming languages, and specifically, high-level procedures and/or object-oriented programming may be used. programming language, and/or assembly/machine language to implement these computational programs. Programming languages include, but are not limited to, languages such as Java, C++, python, "C" or similar programming languages. The program code may execute entirely on the user computing device, partly on the user device, partly on a remote computing device, or entirely on the remote computing device or server. In situations involving remote computing devices, the remote computing devices may be connected to the user computing device through any kind of network, including Local Area Networks (LANs) or Wide Area Networks (WANs), or may be connected to external A computing device (eg, connected via the Internet using an Internet service provider).

In order to better understand the technical solutions provided by the embodiments of the present disclosure, specific examples will be used for description below. Among them, the measured tissue component is blood sugar, the measured area is the forearm extension side of the left arm, and the preset wavelength is 1550 nm. That is, it is verified by in vivo experiments that a tissue composition measurement device with a single preset wavelength combined with a large-area photosensitive surface is used for tissue composition measurement, and the real blood glucose signal that changes synchronously with the blood glucose concentration can be directly obtained.

(1) Preparations before the experiment

1. Measure the parameters of the probe

The measuring probe is provided with M=4 annular photosensitive surfaces, the annular width of each annular photosensitive surface is 0.2 mm, and the 4 annular photosensitive surfaces have the same geometric center. The inner diameters of the four annular photosensitive surfaces from the inside to the outside in the radial direction are the first inner diameter, the second inner diameter, the third inner diameter and the fourth inner diameter, wherein the first inner diameter is 0.8mm, and the second inner diameter is 3.2mm, The third inner diameter is 3.8 mm and the fourth inner diameter is 4.4 mm. The first inner diameter, the second inner diameter, the third inner diameter and the fourth inner diameter all represent diameters.

2. Setting of the regional positioning feature, the first posture positioning feature and the second posture positioning feature

In this specific example, the first gesture location feature and the second gesture location feature are the same, hereinafter referred to as the gesture location feature.

The first is the setting of the pose positioning feature. That is, according to the relationship between the forearm extension side and the bones and muscles between the forearm extension side and the surrounding parts, the setting position of the posture positioning feature is determined. For the forearm extension side, since the change of the wrist state will greatly affect the skin condition of the forearm extension side, in order to improve the positioning accuracy of the measurement posture, a position for setting the positioning feature can be determined on both sides of the wrist. It is the first preset position of the forearm extension side of the left arm close to the elbow joint and the second preset position of the back of the left hand close to the wrist.

In order to reduce the number of posture positioning features required for positioning and measuring posture, a support plane is used for the support of the arm and the palm, and it is required that the arm should be tightly attached to the support plane during the positioning process to limit the rotation of the arm. Therefore, in order to achieve To measure the precise positioning of the posture, it is only necessary to set a posture positioning feature at the selected first preset position and the second preset position respectively. The two posture positioning features can be selected from inherent features on the object to be measured, or can be set manually. In this specific example, they are two manually set posture positioning features, and the two posture positioning features are cross mark points.

Second, the setting of regional positioning features. In order to achieve accurate positioning of the measurement area, a cross mark point is set on the measurement probe as the area positioning feature.

3. Reproducible structure for controllable measurement conditions

The positioning of the measurement area and the positioning of the measurement posture are realized by the optical method. Among them, the positioning of the measurement area and the positioning of the measurement posture are realized based on the positioning unit. Wherein, the positioning part includes a region positioning part and a posture positioning part. The posture positioning part is used to realize the functions of the first posture positioning part and the second posture positioning part, that is, the first posture positioning part and the second posture positioning part are the same posture positioning part. The positioning part and the measuring probe are separate. Both the area positioning part and the posture positioning part use a red laser capable of projecting a cross beam spot.

FIG. 50 schematically shows a schematic diagram of synchronizing the positioning of the measurement area and the positioning of the measurement posture based on an optical method according to an embodiment of the present disclosure.

3. Adjustment of blood sugar concentration

The first method is oral glucose solution. Blood glucose concentration regulation was performed by oral glucose tolerance test (Oral Glucose Tolerance Test, OGTT). The OGTT usually requires the subject to take a glucose solution in which 75 g of glucose is dissolved in 250 ml of water orally. This approach was used for healthy volunteers.

The second way is to eat normally. Blood glucose concentration regulation was performed by oral normal food tolerance test (Meal Torlanrance Test, MTT). MTT usually requires the subjects to take ordinary food with carbohydrates as the mainstay, and a small amount of protein, and to drink as little water as possible or drink high-water drinks, and the total amount of water consumed is less than 50ml. This method is used for volunteers with diabetes.

4. How to obtain the true value of blood sugar

The venous blood was collected from the back of the right hand with a venous indwelling needle and measured by three portable blood glucose meters (GT-1820, Arkray, Japan). The average blood glucose value was taken as the true blood glucose value.

(2) Performance test of the experimental device

The measured signal-to-noise ratio of the standard reflector and the forearm extension side of the test object was measured, and the measured signal-to-noise ratio was compared with the target signal-to-noise ratio to determine the performance of the experimental device. If the measured SNR is lower than the target SNR, the experimental setup is feasible. Among them, the reflectivity of the standard reflector is 40%, and the light intensity values collected by the four annular photosensitive surfaces when measuring the reflector are similar to those when measuring the tissue composition.

For the measurement standard reflector, the logarithmic difference operation is performed on the output light intensity collected by the two annular photosensitive surfaces whose inner diameters are the third inner diameter and the fourth inner diameter, and the differential signal is obtained. 480 data are measured per minute, and the measurement time is 3.5 hours. . The variation of the differential signal during the measurement of the reflector was calculated based on the differential signal at the start of the measurement, and the result is shown in Figure 51. FIG. 51 schematically shows a schematic diagram of a variation of a differential signal obtained by measuring a standard reflective plate according to an embodiment of the present disclosure as a function of measurement duration.

As can be seen from Figure 51, when measuring the reflector, the differential signal fluctuates in the range of about 0.0003a.u. This corresponds to a change in blood glucose concentration of 4.5 mg/dL.

For the forearm extension side of the measured object, the measured object needs to keep an empty stomach when measuring, and the positioning of the measurement area and the measurement posture is realized by an optical method, and during the measurement process, the measurement posture is the target measurement posture. The logarithmic difference operation of the output light intensity collected by the two annular photosensitive surfaces with the inner diameter of the third inner diameter and the fourth inner diameter is carried out to obtain a differential signal, which is calculated based on the differential signal at the end of eating when the blood sugar concentration is stable. The variation of the differential signal during the corresponding variation of the differential signal, the result is shown in Figure 52. Fig. 52 schematically shows a schematic diagram of the variation of the differential signal obtained by measuring the forearm extension side of the subject under a steady state of blood glucose concentration according to an embodiment of the present disclosure as a function of the measurement time.

It can be seen from Figure 52 that during fasting measurement, the differential signal fluctuates within the range of 0.0007a.u., which is equivalent to a blood glucose concentration change of 10.5 mg/dL, which meets the accuracy requirements of blood glucose clinical experiments.

(3) Experimental process

1. Single sugar loading experiment

(1) Experimental arrangement

The tested objects included 10 healthy volunteers and 7 diabetic volunteers, including 11 males and 6 females, and 27 tests were performed on the tested objects.

The age distribution of the subjects included 5 people aged 20 to 30, 4 people aged 30 to 50, and 8 people aged 50 to 72. Among them, 8 people aged 50 to 72 included 6 diabetic patients.

Before the experiment, it is necessary to ensure that the test subjects have fasted for more than 10 hours. The left arm of the object to be measured is placed on the workbench, and the arm can be moved slightly during non-measurement. After the device is warmed up, continuous optical measurement is performed, and the true value of blood glucose is also collected at 5-minute intervals while the optical measurement is performed until the blood glucose concentration of the measured object returns to a lower level. In the process of signal acquisition, the optical method is used to locate the measurement posture.

(2) Data collection

The experiment was divided into a warm-up phase, a feeding phase, and a sugar-loading experimental phase. The warm-up phase is the first 0 to 1 hour of the experiment. During this phase, the measurement probe and the skin will exchange heat until thermal equilibrium is reached. A fasting blood glucose value needs to be collected during the warm-up phase.

After the warm-up phase, the eating phase generally takes ten minutes to eat. At this time, the tested subjects can move slightly. During the period from the end of eating until the end of the measurement, the arm posture of the subject is optically set as the target measurement posture.

The sugar loading experiment phase lasted 1 to 1.5 hours. In this phase, the true value of blood glucose was measured every 5 to 10 minutes, and the measurement signal was recorded at the same time.

(3) Analysis of results

By analyzing the data, it is found that the amplitude of the variation of the average differential signal is about 0.0012 a.u. every time the blood glucose concentration of the measured object changes by 1 mmol/L. At the same time, the change of the differential signal is synchronized with the change of the blood glucose concentration. The correlation coefficient between the two reaches a maximum of 0.96 and an average of 0.80. The corresponding root mean square error of the directly distinguishable blood glucose concentration is at least 0.34 mmol/L, and the average is 0.82. mmol/L.

FIG. 53 schematically shows a schematic diagram of the results of a single sugar loading experiment using the OGTT method according to an embodiment of the present disclosure. Figure 53 is a schematic diagram of the results for a certain measured object. FIG. 54 schematically shows a schematic diagram of the relationship between the variation of the differential signal and the true value of blood glucose according to an embodiment of the present disclosure.

2. Double sugar loading experiment

(1) Experimental arrangement

The test object was a 29-year-old male healthy volunteer. The difference from the single sugar loading experiment is that this experiment requires two meals, that is, after the first sugar loading experiment is completed, the experiment is still continued. The overall experiment lasted about 6 hours, and the rest of the setup was the same as the single sugar loading experiment.

(2) Analysis of results

Analysis of the data proves that the blood glucose signal is obtained, and the variation of the differential signal has a good correlation with the blood glucose concentration. Schematic diagram of the results of double sugar loading experiments in MTT mode. The blood glucose concentration prediction model established by the data obtained from the first MTT can directly predict the blood glucose concentration of the second MTT, and the root mean square error of the prediction reaches 0.68mmol/L. It can be seen that direct mutual prediction can be achieved under the condition that the two MTTs maintain the same measurement conditions, and the result is shown in FIG. 56 , which schematically shows a blood glucose prediction value and a blood glucose true value according to an embodiment of the present disclosure. Schematic diagram of the relationship between values. The blood glucose prediction value in FIG. 56 shows the result of predicting the blood glucose concentration of the second MTT by using the blood glucose concentration prediction model established by the data obtained from the first MTT.

To sum up, according to the correlation between the variation of the differential signal and the blood glucose concentration in the single sugar loading experiment of 27 people, and compared with the data of the control group, it is confirmed that a single preset wavelength combined with a large-area photosensitive surface is used. The tissue composition measuring device measures the tissue composition, and directly obtains the real blood glucose signal. At the same time, the importance and validity of the three principles of tissue composition measurement are also confirmed.

The flowchart and block diagrams in the Figures illustrate the architecture, functionality, and operation of possible implementations of systems, methods and computer program products according to various embodiments of the present disclosure. In this regard, each block in the flowchart or block diagrams may represent a module, segment, or portion of code that contains one or more logical functions for implementing the specified functions executable instructions. It should also be noted that, in some alternative implementations, the functions noted in the blocks may occur out of the order noted in the figures. For example, two blocks shown in succession may, in fact, be executed substantially concurrently, or the blocks may sometimes be executed in the reverse order, depending upon the functionality involved. It is also noted that each block of the block diagrams or flowchart illustrations, and combinations of blocks in the block diagrams or flowchart illustrations, can be implemented in special purpose hardware-based systems that perform the specified functions or operations, or can be implemented using A combination of dedicated hardware and computer instructions is implemented. Those skilled in the art will appreciate that various combinations and/or combinations of features recited in various embodiments and/or claims of the present disclosure are possible, even if such combinations or combinations are not expressly recited in the present disclosure. In particular, various combinations and/or combinations of the features recited in the various embodiments of the present disclosure and/or in the claims may be made without departing from the spirit and teachings of the present disclosure. All such combinations and/or combinations fall within the scope of this disclosure.

Embodiments of the present disclosure have been described above. However, these examples are for illustrative purposes only, and are not intended to limit the scope of the present disclosure. Although the various embodiments are described above separately, this does not mean that the measures in the various embodiments cannot be used in combination to advantage. The scope of the present disclosure is defined by the appended claims and their equivalents. Without departing from the scope of the present disclosure, those skilled in the art can make various substitutions and modifications, and these substitutions and modifications should all fall within the scope of the present disclosure.

Claims

A method for measuring tissue composition comprising:

irradiating the measurement area with incident light of a single preset wavelength, wherein each beam of the incident light passes through the measurement area and then emerges from at least one exit position to form at least one beam of exit light, and the incident position of the incident light includes at least one;

Obtain the light intensity values corresponding to each beam of the outgoing light collected by the M photosensitive surfaces, and obtain T output light intensities, wherein each of the output light intensities is collected according to one or more of the photosensitive surfaces The light intensity value of the outgoing light is obtained by processing, and each photosensitive surface can collect the light intensity value of the outgoing light emitted from the outgoing position within the preset anti-shake range corresponding to the photosensitive surface, 1≤T ≤M; and

The concentration of the measured tissue component is determined according to at least one output light intensity corresponding to the preset wavelength.
The method according to claim 1, wherein the ratio of the average optical length of the outgoing light received by each of the photosensitive surfaces in the target tissue layer to the total optical length is greater than or equal to a proportional threshold, wherein the total optical length is the total distance that the outgoing light travels in the measurement area.
The method according to claim 1 or 2, further comprising:

The total area of the photosensitive surfaces of the same type is determined according to the tissue structure features in the measurement area, wherein the photosensitive surfaces of the same type include one or more photosensitive surfaces, and the photosensitive surfaces of the same type are used to output one output light intensity.
The method of claim 1 or 2, wherein a ratio of the area of each of the photosensitive surfaces to the perimeter of the photosensitive surfaces is greater than or equal to a ratio threshold.
5. The method of claim 4, wherein the ratio threshold is greater than or equal to 0.04 mm.
The method of claim 1 or 2, wherein the photosensitive surface is in contact or non-contact with the surface of the measurement area.
6. The method of claim 6, wherein the distance of the photosensitive surface from the surface of the measurement region is less than or equal to a first distance threshold and the efficiency of the photosensitive surface in receiving outgoing light is greater than or equal to an efficiency threshold.
The method of claim 1, wherein before said irradiating the measurement area with the incident light of a single preset wavelength, further comprising:

determine positioning features;

determining the measurement area based on the location feature, wherein the measurement area is an area that satisfies reproducibility of controllable measurement conditions; and

A measurement probe is arranged at a position corresponding to the measurement area, wherein the measurement probe includes the M photosensitive surfaces.
The method of claim 6, wherein the positioning features include a first posture positioning feature and an area positioning feature;

The determining the measurement area according to the positioning feature includes:

adjusting the current measurement posture of the measured object to a target measurement posture according to the first posture positioning feature, wherein the target measurement posture is a measurement posture that satisfies the reproducibility of the controllable measurement condition; and

When the current measurement posture is the target measurement posture, the measurement area is determined according to the area positioning feature.
The method according to claim 9, wherein the disposing the measurement probe at a position corresponding to the measurement area comprises:

The measurement probe is arranged at a position corresponding to the measurement area by a fixing part, wherein the fixing part and the measurement probe are integrated, partially separated or completely separated.
The method of claim 10, wherein the fixing part comprises a fixing seat and a first fitting;

The setting of the measurement probe at a position corresponding to the measurement area by the fixing part includes:

The fixing seat is arranged at a position corresponding to the measurement area by the first fitting; and

The measuring probe is set on the fixing seat.
11. The method of claim 11, wherein the skin condition of the skin at the measurement area satisfies a first pre-condition during the process of disposing the fixing seat at the position corresponding to the measurement area by the first fitting member Set conditions.
The method according to claim 11, wherein the skin state of the skin at the measurement area satisfies a second preset condition during the process of disposing the measurement probe on the fixing seat.
11. The method of claim 11, wherein the measurement probe does not move in the mount.
The method of claim 10, wherein the fixing portion comprises a second fitting;

The setting of the measurement probe at a position corresponding to the measurement area by the fixing part includes:

The measurement probe is set at a position corresponding to the measurement area through the second fitting.
16. The method of claim 15, wherein the skin condition of the skin at the measurement area satisfies a third pre-determination during the process of setting the measurement probe at a position corresponding to the measurement area by the second fitting. Set conditions.
The method according to claim 10, wherein the determining the measurement area according to the area positioning feature comprises:

Obtain the first projection feature;

In the case that it is determined that the regional positioning feature does not match the first projection feature, adjusting the position of the measuring probe and/or the fixing portion until the regional positioning feature matches the first projection feature; as well as

In the case where it is determined that the region positioning feature matches the first projection feature, the region corresponding to the measurement probe and/or the fixing portion is determined as the measurement region.
The method according to claim 10, wherein the determining the measurement area according to the area positioning feature comprises:

obtain the first target image;

acquiring a first template image, wherein the first template image includes the region positioning feature;

In the case that it is determined that the first target image does not match the first template image, adjust the position of the measuring probe and/or the fixing part to acquire a new first target image until the new a first target image is matched to the first template image; and

When it is determined that the first target image matches the first template image, an area corresponding to the measurement probe and/or the fixing portion is determined as the measurement area.
The method according to claim 10, wherein the determining the measurement area according to the area positioning feature comprises:

acquiring a second target image, wherein the second target image includes the region positioning feature;

In the case where it is determined that the position of the region positioning feature in the second target image is not the first preset position, adjust the position of the measuring probe and/or the fixing part to obtain a new second target image , until the position of the region positioning feature in the new second target image is the first preset position; and

When it is determined that the position of the region positioning feature in the new second target image is the first preset position, the region corresponding to the measurement probe and/or the fixing part is determined as the first preset position Measurement area.
The method according to claim 10, wherein the adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature comprises:

Get the second projection feature;

if it is determined that the first pose location feature does not match the second projected feature, adjusting the current measurement pose until the first pose location feature matches the second projected feature; and

In a case where it is determined that the first posture positioning feature matches the second projection feature, it is determined that the current measurement posture is the target measurement posture.
The method according to claim 10, wherein the adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature comprises:

Get the third target image;

acquiring a second template image, wherein the second template image includes the first posture positioning feature;

In the case that it is determined that the third target image does not match the second template image, the current measurement posture is adjusted to obtain a new third target image, until the new third target image matches the first two-template image matching; and

When it is determined that the new third target image matches the second template image, it is determined that the current measurement posture is the target measurement posture.
The method according to claim 10, wherein the adjusting the current measurement posture of the measured object to the target measurement posture according to the first posture positioning feature comprises:

acquiring a fourth target image, wherein the fourth target image includes the first posture positioning feature;

In the case where it is determined that the position of the first posture positioning feature in the fourth target image is not at the second preset position, adjust the current measurement posture to obtain a new fourth target image, until the new fourth target image is The position of the first gesture positioning feature in the four-target image is at the second preset position; and

When it is determined that the position of the first posture positioning feature in the new fourth target image is at the second preset position, the current measurement posture is determined to be the target measurement posture.
The method of claim 10, further comprising:

If the measurement probe is disposed at a position corresponding to the measurement area, determining a second posture positioning feature when it is determined that the current measurement posture is not the target measurement posture; and

According to the second posture positioning feature, the current measurement posture is adjusted to the target measurement posture.
The method according to claim 23, wherein the adjusting the current measurement posture to the target measurement posture according to the second posture positioning feature comprises:

Get the third projection feature;

if it is determined that the second pose location feature does not match the third projected feature, adjusting the current measurement pose until the second pose location feature matches the third projected feature; and

In a case where it is determined that the second posture positioning feature matches the third projection feature, it is determined that the current measurement posture is the target measurement posture.
The method according to claim 23, wherein the adjusting the current measurement posture to the target measurement posture according to the second posture positioning feature comprises:

Get the fifth target image;

acquiring a third template image, wherein the third template image includes the second posture positioning feature;

In the case where it is determined that the fifth target image does not match the third template image, the current measurement posture is adjusted to obtain a new fifth target image until the new fifth target image matches the third template image. three-template image matching; and

When it is determined that the new fifth target image matches the third template image, the current measurement posture is determined to be the target measurement posture.
The method according to claim 23, wherein the adjusting the current measurement posture to the target measurement posture according to the second posture positioning feature comprises:

acquiring a sixth target image, wherein the sixth target image includes the second posture positioning feature;

In the case where it is determined that the position of the second posture positioning feature in the sixth target image is not at the third preset position, adjust the current measurement posture to acquire a new sixth target image until the new sixth target image is The position of the second posture positioning feature in the six target images is at the third preset position; and

When it is determined that the position of the second posture positioning feature in the new sixth target image is at the third preset position, the current measurement posture is determined to be the target measurement posture.
The method of claim 23, further comprising:

Prompt information is generated, wherein the prompt information is used to prompt the completion of the measurement posture positioning and/or the measurement area positioning, and the prompt information is in the form of at least one of image, voice or vibration.
The method of claim 11, further comprising:

In the case where it is determined that the fixing seat is arranged at a position corresponding to the measurement area and the measuring probe is not arranged on the fixing portion, the measuring probe is arranged on the fixing seat;

When it is determined that the fixing seat is not arranged at the position corresponding to the measurement area, the fixing seat is arranged at the position corresponding to the measurement area through the first fitting, and the measurement probe is arranged on the fixed seat.
The method of claim 15, further comprising:

When it is determined that the measurement probe is not arranged at the position corresponding to the measurement area, the measurement probe is arranged at the position corresponding to the measurement area through the second fitting.
The method according to claim 1, wherein the determining the concentration of the measured tissue component according to at least one output light intensity corresponding to the preset wavelength comprises:

determining a first output light intensity and a second output light intensity from at least two output light intensities corresponding to the preset wavelengths; and

The concentration of the measured tissue component is determined according to the first output light intensity and the second output light intensity corresponding to the preset wavelength.
The method according to claim 30, wherein the determining the concentration of the measured tissue component according to the first output light intensity and the second output light intensity corresponding to the preset wavelength comprises:

performing differential processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal; and

The concentration of the measured tissue component is determined according to the differential signal corresponding to the preset wavelength.
The method according to claim 31, wherein performing differential processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal, comprising:

A differential circuit is used to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain the differential signal.
The method according to claim 31, wherein performing differential processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain a differential signal, comprising:

A differential algorithm is used to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain the differential signal.
The method according to claim 33, wherein the using a differential algorithm to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain the differential signal comprises:

The differential signal is obtained by performing a direct differential operation on the first output light intensity and the second output light intensity corresponding to the preset wavelength.
The method according to claim 33, wherein the using a differential algorithm to process the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain the differential signal comprises:

Perform logarithmic processing on the first output light intensity and the second output light intensity corresponding to the preset wavelength to obtain the first logarithmic light intensity and the second logarithmic light intensity; and

The differential signal is obtained by performing a direct differential operation on the first logarithmic light intensity and the second logarithmic light intensity corresponding to the preset wavelength.
The method according to claim 31, wherein the determining the concentration of the measured tissue component according to the differential signal corresponding to the preset wavelength comprises:

The differential signal corresponding to the preset wavelength is input into the first tissue component concentration prediction model, and the concentration of the measured tissue component is output.
The method of claim 36, further comprising:

Obtain a first training sample set, wherein the first training sample set includes a plurality of first training samples, wherein each of the first training samples includes the first true concentration of the measured tissue component and the a differential signal corresponding to the first true concentration; and

According to the first training sample set, the first tissue component concentration prediction model is established.
The method according to claim 37, wherein the establishing the first tissue component concentration prediction model according to the first training sample set comprises:

Preprocessing the first training sample set to obtain a processed first training sample set; and

The first tissue component concentration prediction model is established according to the processed first training sample set.
The method of claim 36, further comprising:

Under the condition that the fourth preset condition is satisfied, the first tissue component concentration prediction model is modified to process the new differential signal by using the revised first tissue component concentration prediction model to obtain a new measured tissue component concentration prediction model. concentration.
The method of claim 39, wherein the modifying the first tissue component concentration prediction model comprises:

obtaining the first target concentration of the measured tissue component;

obtaining a differential signal corresponding to the first target concentration; and

The first tissue component concentration prediction model is corrected based on the difference signal corresponding to the first target concentration and the first target concentration.
The method of claim 36, further comprising:

Under the condition that the fifth preset condition is satisfied, the new differential signal is processed by using the new first tissue component concentration prediction model to obtain a new measured tissue component concentration.
The method according to claim 31, wherein the determining the concentration of the measured tissue component according to the differential signal corresponding to the preset wavelength comprises:

obtaining a current interference parameter value for each of the plurality of interference parameters; and

A plurality of the current interference parameter values and the differential signals corresponding to the preset wavelengths are input into the second tissue component concentration prediction model, and the concentration of the measured tissue component is output.
The method of claim 42, further comprising:

Obtain a second training sample set, wherein the second training sample set includes a plurality of second training samples, wherein each of the second training samples includes the second true concentration of the tested tissue component and the the differential signal corresponding to the second real concentration;

Obtain a third training sample set, wherein the third training sample set includes a plurality of third training samples, wherein each of the third training samples includes a training interference parameter of each of the plurality of interference parameters value and a differential signal corresponding to each of said training disturbance parameter values;

According to the second training sample set, establish a tissue component concentration prediction model to be corrected;

establishing a correction parameter model according to the third training sample set; and

According to the tissue component concentration prediction model to be corrected and the correction parameter model, the second tissue component concentration prediction model is obtained.
The method of claim 42, further comprising:

Under the condition that the fourth preset condition is satisfied, the second tissue component concentration prediction model is revised, so as to use the revised second tissue component concentration prediction model to process the new differential signal and the new multiple current interference parameter values , to obtain the new concentration of the measured tissue component.
The method of claim 44, wherein the modifying the second tissue component concentration prediction model comprises:

obtaining the second target concentration of the measured tissue component;

acquiring a differential signal corresponding to the second target concentration;

obtaining a current interference parameter value for each of the plurality of interference parameters; and

The second tissue component concentration prediction model is revised based on the second target concentration, a plurality of the interference parameter values, and a differential signal corresponding to the second target concentration.
The method of claim 42, further comprising:

Under the condition that the fifth preset condition is satisfied, the new differential signal and the new multiple current interference parameter values are processed by using the new second tissue component concentration prediction model to obtain a new measured tissue component concentration.
The method according to claim 31, wherein the first output light intensity and the second output light intensity are collected by the same or different photosensitive surfaces of the same type at different times, wherein the first output light intensity The intensity is the light intensity in systole, the second output light intensity is light intensity in diastole, and the photosensitive surfaces of the same type include one or more photosensitive surfaces, and the photosensitive surfaces of the same type are used to output one output light intensity.
The method according to claim 31 , wherein the first output light intensity corresponding to the preset wavelength is collected by a first photosensitive surface of the same type corresponding to the preset wavelength, which corresponds to the preset wavelength. The second output light intensity is obtained from the second photosensitive surface of the same type corresponding to the preset wavelength, wherein the first photosensitive surface of the same type includes one or more of the photosensitive surfaces, and the second photosensitive surface of the same type The face includes one or more of the photosensitive faces.
48. The method of claim 48, wherein the first homogeneous photosensitive surface and the second homogeneous photosensitive surface are the same homogeneous photosensitive surface, and the first homogeneous photosensitive surface and the second homogeneous photosensitive surface receive The outgoing light is obtained by transmitting the incident light from different incident positions.
49. The method of claim 48, wherein the first homogeneous photosensitive surface and the second homogeneous photosensitive surface are different homogeneous photosensitive surfaces.
The method according to claim 48, wherein the average optical length of the outgoing light received by different photosensitive positions of each of the photosensitive surfaces in the first same type of photosensitive surface belongs to a first average optical length range, wherein the The first average optical path range is determined according to the first optical path average value, and the first optical path average value is calculated according to the average optical path length of the outgoing light received by each of the photosensitive positions of the first similar photosensitive surfaces the average obtained;

The average optical length of the outgoing light received by different photosensitive positions of each of the photosensitive surfaces of the second same type belongs to the second average optical path range, wherein the second average optical path range is based on the second light path. The second optical path average value is an average value calculated according to the average optical path length of the outgoing light received by each of the photosensitive positions of the second photosensitive surface of the same type.
The method of claim 51, wherein the absolute value of the difference between the first optical path average value and the second optical path average value belongs to a first optical path difference range.
The method of claim 52, wherein the first average optical path range is less than or equal to the first optical path difference range and the second average optical path range is less than or equal to the first optical path difference range .
The method of claim 52, wherein the first optical path difference range is determined according to an optimal differential optical path corresponding to the preset wavelength.
The method according to claim 48, wherein the source-detection distance of each of the photosensitive surfaces of the first same type of photosensitive surfaces corresponding to the preset wavelengths from the center of the incident light is in the range corresponding to the preset wavelength. The preset source detection distance range is determined according to the source detection distance between the floating reference position corresponding to the preset wavelength and the center of the incident light.
The method according to claim 1, wherein the determining the concentration of the measured tissue component according to at least one output light intensity corresponding to the preset wavelength comprises:

determining a third output light intensity from at least one output light intensity corresponding to the preset wavelength; and

The concentration of the measured tissue component is determined according to the third output light intensity corresponding to the preset wavelength.
The method according to claim 56, wherein the third output light intensity corresponding to the preset wavelength is collected from the same type of photosensitive surface corresponding to the preset wavelength, and each of the same type of photosensitive surface The difference between the average optical length of the outgoing light received by different photosensitive positions on the photosensitive surface and the optimal optical length corresponding to the preset wavelength belongs to the second optical path difference range.
The method according to claim 56, wherein the determining the concentration of the measured tissue component according to the third output light intensity corresponding to the preset wavelength comprises:

The third output light intensity corresponding to the preset wavelength is input into a third tissue component concentration prediction model, and the measured tissue component concentration is output.
The method according to claim 1 or 2, wherein each of the photosensitive surfaces comprises an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of different photosensitive surfaces are the same or different.
The method of claim 59, wherein the non-annular photosensitive surface comprises a fan ring photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.
The method of claim 60, wherein the polygonal photosensitive surface comprises a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.
59. The method of claim 59, wherein the homogeneous photosensitive surface comprises the annular photosensitive surface or the non-annular photosensitive surface, wherein the homogeneous photosensitive surface comprises one or more of the photosensitive surfaces, the homogeneous photosensitive surface The photosensitive surface is used to output one of the output light intensity.
The method of claim 62, wherein the same type of photosensitive surface is the annular photosensitive surface, comprising:

In the case that the photosensitive surfaces of the same type include one photosensitive surface, the photosensitive surfaces of the same type are independent annular photosensitive surfaces;

When the photosensitive surfaces of the same type include a plurality of the photosensitive surfaces, the photosensitive surfaces of the same type are annular photosensitive surfaces formed according to the combination of the plurality of photosensitive surfaces;

The same type of photosensitive surface is the non-annular photosensitive surface, including:

In the case that the photosensitive surfaces of the same type include one photosensitive surface, the photosensitive surfaces of the same type are independent non-ring photosensitive surfaces;

When the photosensitive surfaces of the same type include a plurality of the photosensitive surfaces, the photosensitive surfaces of the same type are non-annular photosensitive surfaces formed by combining the plurality of photosensitive surfaces.
The method according to claim 63, wherein, when it is determined that the distance between the photosensitive surfaces of the same type from the target site is greater than or equal to the second distance threshold, the photosensitive surfaces of the same type include a ring photosensitive surface, a fan ring photosensitive surface, a fan-shaped photosensitive surface, and a fan-shaped photosensitive surface. Photosensitive surface, round photosensitive surface or square photosensitive surface.
The method according to claim 63, wherein in the case where it is determined that the distance between the same type of photosensitive surface and the target site is less than or equal to a third distance threshold, the shape of the same type of photosensitive surface is based on the output light. Jitter distribution is determined.
66. The method of claim 65, wherein the jitter distribution of the outgoing light comprises decomposition into a jitter distribution in a first direction and a jitter distribution in a second direction, the first direction and the second direction Perpendicular to each other, the ratio of the length of the same photosensitive surface along the first direction to the length of the same photosensitive surface along the second direction is based on the jitter amplitude of the emitted light along the first direction and the Determined by the ratio of the shaking amplitude of the outgoing light along the second direction, the shaking amplitude of the outgoing light along the first direction is the largest.
The method of claim 66 , wherein the same type of photosensitive surface comprises a rectangular photosensitive surface or an elliptical photosensitive surface, and the ratio of the length to the width of the rectangular photosensitive surface is determined according to the emitted light along the first direction. Determined by the ratio of the jitter amplitude to the jitter amplitude of the outgoing light along the second direction, and the ratio of the long axis to the short axis of the elliptical photosensitive surface is based on the outgoing light along the first direction is determined by the ratio of the jitter amplitude to the jitter amplitude of the outgoing light along the second direction.
The method according to claim 1 or 2, wherein each of the output light intensity is obtained by processing according to the light intensity value of the outgoing light collected by one or more of the photosensitive surfaces, comprising:

using said one or more photosensitive surfaces in combination to output one said output light intensity; or

In the case where each photosensitive surface of the one or more photosensitive surfaces is used independently, one output light intensity is obtained by calculating the light intensity value of the outgoing light collected by each of the photosensitive surfaces.
The method according to claim 1 or 2, wherein the determining the concentration of the measured tissue component according to at least one output light intensity corresponding to the preset wavelength comprises:

determining at least one superimposed light intensity corresponding to the preset wavelength, wherein the superimposed light intensity is obtained by adding a plurality of output light intensities corresponding to the preset wavelength; and

The concentration of the measured tissue component is determined according to at least one superimposed light intensity corresponding to the preset wavelength.
The method according to claim 1 or 2, wherein the preset wavelength is a wavelength sensitive to the measured tissue composition.
The method of claim 1 or 2, wherein the temperature of the measurement region is maintained within a preset temperature range during tissue composition measurement.
The method according to claim 1 or 2, wherein the photosensitive surface is obtained after setting a mask on the initial photosensitive surface, and the light transmittance of the mask is less than or equal to a light transmittance threshold.
The method of claim 72, wherein the shape of the mask is determined according to the shape of the jitter distribution of the outgoing light.
The method according to claim 1 or 2, wherein the intensity distribution of the light spot irradiated by the incident light to the measurement area is uniform.
The method according to claim 1 or 2, wherein the area of the light spot irradiated by the incident light to the measurement region is greater than or equal to a light spot area threshold.
A tissue composition measurement device, comprising:

A light source module for irradiating the measurement area with incident light of a single preset wavelength, wherein each beam of the incident light passes through the measurement area and exits from at least one exit position to form at least one beam of outgoing light. The location includes at least one;

a collection module, the collection module includes M photosensitive surfaces, and each of the photosensitive surfaces can collect the light intensity value of the outgoing light emitted from the outgoing position within the preset anti-shake range corresponding to the photosensitive surface, The acquisition module is configured to acquire the light intensity values corresponding to each beam of the outgoing light collected by the M photosensitive surfaces, and obtain T output light intensities, wherein each of the output light intensities is based on one or more of the output light intensities. obtained by processing the light intensity values of the outgoing lights collected by the photosensitive surfaces, 1≤T≤M; and

The processing module is configured to determine the concentration of the measured tissue component according to at least one output light intensity corresponding to the preset wavelength.
The device according to claim 76, wherein the ratio of the average optical length of the outgoing light received by each of the photosensitive surfaces in the target tissue layer to the total optical length is greater than or equal to a proportional threshold, wherein the total optical length is the total distance that the outgoing light travels in the measurement area.
The device according to claim 76 or 77, wherein the total area of the photosensitive surfaces of the same type is determined according to the characteristics of the tissue structure in the measurement area, wherein the photosensitive surfaces of the same type include one or more photosensitive surfaces, The photosensitive surfaces of the same type are used to output one of the output light intensity.
76 or 77, wherein the ratio of the area of each of the photosensitive surfaces to the perimeter of the photosensitive surfaces is greater than or equal to a ratio threshold.
79. The apparatus of claim 79, wherein the ratio threshold is greater than or equal to 0.04 mm.
The device of claim 76 or 77, wherein the photosensitive surface is in contact or non-contact with the surface of the measurement area.
81. The device of claim 81, wherein a distance of the photosensitive surface from the surface of the measurement region is less than or equal to a first distance threshold and the photosensitive surface receives outgoing light with an efficiency greater than or equal to an efficiency threshold.
The apparatus of claim 76, further comprising:

a first determination module, used for determining the positioning feature;

a second determination module, configured to determine the measurement area according to the positioning feature, wherein the measurement area is an area that satisfies the reproducibility of controllable measurement conditions; and

The setting module is used for setting the measurement probe at a position corresponding to the measurement area, wherein the measurement probe includes the M photosensitive surfaces.
83. The apparatus of claim 83, wherein the locating features include a first gesture locating feature and a region locating feature;

The second determining module includes:

a first adjustment unit, configured to adjust the current measurement posture of the measured object to a target measurement posture according to the first posture positioning feature, wherein the target measurement posture is a measurement posture that satisfies the reproducibility of the controllable measurement conditions ;as well as

A first determining unit, configured to determine the measurement area according to the area positioning feature when the current measurement posture is the target measurement posture.
The device of claim 84, further comprising a fixing portion for disposing the measurement probe at a position corresponding to the measurement area, wherein the fixing portion is integral with the measurement probe , partially discrete or fully discrete.
The device of claim 85, wherein the fixing portion comprises a fixing seat and a first fitting;

the first fitting part, used for disposing the fixing seat at a position corresponding to the measurement area; and

The fixing seat is used for fixing the measuring probe.
86. The device of claim 86, wherein the hardness of the first fitting includes a first hardness and a second hardness, wherein the first hardness is less than the second hardness, the first hardness being the The hardness corresponding to the first fitting piece in the process of fixing the fixing base, and the second hardness is the hardness corresponding to the fixing base by the first fitting piece.
87. The device of claim 87, wherein the first fitting comprises a first Velcro or a first elastic band.
88. The device of claim 87, wherein the hardness of the first fitting is greater than or equal to a first hardness threshold and less than or equal to a second hardness threshold.
The device according to claim 86, further comprising a first magnetic part, all or part of the first fitting part is a metal hinge, and the first magnetic part cooperates with the first fitting part to fix the fixing seat .
The device of claim 86, wherein the surface of the first fitting is provided with holes.
The device of claim 86, wherein the measurement probe is secured to the mount by at least one of the following:

The measuring probe is fixed on the fixing seat by adhesive tape;

the measuring probe is fixed on the fixing seat by a fastener;

the measuring probe is fixed on the fixing seat by magnetic force;

The friction coefficient between the measuring probe and the fixed seat is greater than or equal to a friction coefficient threshold.
The device of claim 85, wherein the fixing portion comprises a second fitting;

The second matching part is used to set the measurement probe at a position corresponding to the measurement area.
93. The device of claim 93, wherein the hardness of the second fitting includes a third hardness and a fourth hardness, wherein the third hardness is less than the fourth hardness, the third hardness being the The hardness corresponding to the second fitting piece in the process of fixing the measuring probe, and the fourth hardness is the hardness corresponding to the second fitting piece fixing the measuring probe.
94. The device of claim 94, wherein the second fitting comprises a second Velcro or a second elastic band.
94. The device of claim 94, wherein the hardness of the second fitting is greater than or equal to a third hardness threshold and less than or equal to a fourth hardness threshold.
The device according to claim 93, further comprising a second magnetic part, all or part of the second fitting part is a metal hinge, and the second magnetic part cooperates with the second fitting part to fix the measuring probe .
The device of claim 93, wherein the surface of the second fitting is provided with holes.
The apparatus according to claim 85, wherein the first determining unit is configured to:

Obtain the first projection feature;

In the case that it is determined that the regional positioning feature does not match the first projection feature, adjusting the position of the measuring probe and/or the fixing portion until the regional positioning feature matches the first projection feature; as well as

In the case where it is determined that the region positioning feature matches the first projection feature, the region corresponding to the measurement probe and/or the fixing portion is determined as the measurement region.
The device according to claim 99, further comprising an area positioning part, the area positioning part is arranged on the measured object, the measuring probe, the fixing part or other objects, and the area positioning part is used for projecting the Describe the first projection feature.
The apparatus according to claim 100, wherein, in the case where it is determined that the area locating portion is provided on the measurement probe, the area locating feature is not provided on the measurement probe;

When it is determined that the area positioning portion is provided on the fixing portion, the area positioning feature is not provided on the fixing portion.
100. The apparatus of claim 100, wherein the area locator comprises a first laser.
The apparatus according to claim 85, wherein the first determining unit is configured to:

obtain the first target image;

acquiring a first template image, wherein the first template image includes the region positioning feature;

In the case that it is determined that the first target image does not match the first template image, adjust the position of the measuring probe and/or the fixing part to acquire a new first target image until the new a first target image is matched to the first template image; and

When it is determined that the first target image matches the first template image, an area corresponding to the measurement probe and/or the fixing portion is determined as the measurement area.
The device according to claim 103, further comprising a first image acquisition part, the first image acquisition part is arranged on the measured object, the measurement probe, the fixed part or other objects, the first image The acquisition part is used for acquiring the first target image.
The apparatus according to claim 85, wherein the first determining unit is configured to:

acquiring a second target image, wherein the second target image includes the region positioning feature;

In the case where it is determined that the position of the region positioning feature in the second target image is not the first preset position, adjust the position of the measuring probe and/or the fixing part to obtain a new second target image , until the position of the region positioning feature in the new second target image is the first preset position; and

When it is determined that the position of the region positioning feature in the new second target image is the first preset position, the region corresponding to the measurement probe and/or the fixing part is determined as the first preset position Measurement area.
The device according to claim 105, further comprising a second image acquisition part, the second image acquisition part is arranged on the measured object, the measurement probe, the fixed part or other objects, the second image The acquisition part is used for acquiring the second target image.
The apparatus according to claim 106, wherein, in the case where it is determined that the second image acquisition part is provided on the measurement probe, the area positioning feature is not provided on the measurement probe;

In a case where it is determined that the second image capturing part is arranged on the fixing part, the region positioning feature is not arranged on the fixing part.
The apparatus of claim 85, wherein the first adjustment unit is configured to:

Get the second projection feature;

if it is determined that the first pose location feature does not match the second projected feature, adjusting the current measurement pose until the first pose location feature matches the second projected feature; and

In a case where it is determined that the first posture positioning feature matches the second projection feature, it is determined that the current measurement posture is the target measurement posture.
The device according to claim 109, further comprising a first posture positioning part, the first posture positioning part is arranged on the measured object, the measurement probe, the fixing part or other objects, the first posture The positioning part is used for projecting the second projection feature.
The apparatus according to claim 109, wherein, in the case where it is determined that the first posture locating portion is provided on the measurement probe, the first posture locating feature is not provided on the measurement probe;

When it is determined that the first posture positioning portion is provided on the fixing portion, the first posture positioning feature is not provided on the fixing portion.
109. The apparatus of claim 109, wherein the first posture locator comprises a second laser.
The apparatus of claim 85, wherein the first adjustment unit is configured to:

Get the third target image;

acquiring a second template image, wherein the second template image includes the first posture positioning feature;

In the case that it is determined that the third target image does not match the second template image, the current measurement posture is adjusted to obtain a new third target image, until the new third target image matches the first two-template image matching; and

When it is determined that the new third target image matches the second template image, it is determined that the current measurement posture is the target measurement posture.
The device according to claim 112, further comprising a third image acquisition part, the third image acquisition part is arranged on the measured object, the measurement probe, the fixed part or other objects, the third image acquisition part The acquisition part is used for acquiring the third target image.
The apparatus of claim 85, wherein the first adjustment unit is configured to:

acquiring a fourth target image, wherein the fourth target image includes the first posture positioning feature;

In the case where it is determined that the position of the first posture positioning feature in the fourth target image is not at the second preset position, adjust the current measurement posture to obtain a new fourth target image, until the new fourth target image is The position of the first gesture positioning feature in the four-target image is at the second preset position; and

When it is determined that the position of the first posture positioning feature in the new fourth target image is at the second preset position, the current measurement posture is determined to be the target measurement posture.
The device according to claim 114, further comprising a fourth image acquisition part, the fourth image acquisition part is arranged on the measured object, the measurement probe, the fixed part or other objects, the fourth image The acquisition part is used for acquiring the fourth target image.
The apparatus according to claim 115, wherein, in the case where it is determined that the fourth image acquisition part is provided on the measurement probe, the first posture positioning feature is not provided on the measurement probe;

In a case where it is determined that the fourth image capturing part is provided on the fixing part, the first posture positioning feature is not provided on the fixing part.
The apparatus of claim 85, further comprising:

a third determining module, configured to determine a second posture positioning feature when the current measurement posture is not the target measurement posture if the measurement probe is set at a position corresponding to the measurement area; and

An adjustment module, configured to adjust the current measurement posture to the target measurement posture according to the second posture positioning feature.
The apparatus of claim 117, wherein the adjustment module comprises:

a first acquiring unit, used for acquiring a third projection feature;

a second adjustment unit, configured to adjust the current measurement posture when it is determined that the second posture locating feature does not match the third projection feature until the second posture locating feature matches the third projection feature matching; and

A second determining unit, configured to determine the current measurement posture as the target measurement posture when it is determined that the second posture positioning feature matches the third projection feature.
The device according to claim 118, further comprising a second posture positioning part, the second posture positioning part is provided on the measured object, the measuring probe, the fixing part or other objects, the second posture The positioning part is used for projecting the third projection feature.
The apparatus of claim 119, wherein, in a case where it is determined that the second posture positioning portion is provided on the measurement probe, the second posture positioning feature is not provided on the measurement probe and the fixing portion;

When it is determined that the second posture positioning portion is provided on the fixing portion, the second posture positioning feature is not provided on the measuring probe and the fixing portion.
120. The apparatus of claim 120, wherein the second posture locator comprises a third laser.
The apparatus of claim 117, wherein the adjustment module comprises:

a second acquisition unit, used for acquiring the fifth target image;

a third acquiring unit, configured to acquire a third template image, wherein the third template image includes the second posture positioning feature;

a third adjustment unit, configured to adjust the current measurement posture to obtain a new fifth target image when it is determined that the fifth target image does not match the third template image, until the new Five target images are matched with the third template image; and

A third determining unit, configured to determine the current measurement posture as the target measurement posture when it is determined that the new fifth target image matches the third template image.
The device according to claim 122, further comprising a fifth image acquisition part, the fifth image acquisition part is arranged on the measured object, the measurement probe, the fixed part or other objects, the fifth image The acquisition part is used for acquiring the fifth target image.
The apparatus of claim 117, wherein,

The adjustment module includes:

a fourth acquisition unit, configured to acquire a sixth target image, wherein the sixth target image includes the second posture positioning feature;

a fourth adjustment unit, configured to adjust the current measurement posture to obtain a new sixth target image when it is determined that the position of the second posture positioning feature in the sixth target image is not at the third preset position , until the position of the second gesture positioning feature in the new sixth target image is at the third preset position; and

a fourth determining unit, configured to determine that the current measurement posture is the target measurement when it is determined that the position of the second posture positioning feature in the new sixth target image is at the third preset position posture.
The device according to claim 124, further comprising a sixth image acquisition part, the sixth image acquisition part is arranged on the measured object, the measurement probe, the fixed part or other objects, the sixth image The acquisition part is used for acquiring the sixth target image.
The apparatus according to claim 125, wherein, in the case where it is determined that the sixth image acquisition part is provided on the measurement probe, the second posture positioning feature is not provided on the measurement probe and the fixing part;

In a case where it is determined that the sixth image capturing part is provided on the fixing part, the second posture positioning feature is not provided on the measuring probe and the fixing part.
The apparatus of claim 117, further comprising:

The prompting module is configured to generate prompting information, wherein the prompting information is used to prompt the completion of the measurement posture positioning and/or the measurement area positioning, and the prompting information includes at least one of image, voice or vibration.
The device according to claim 76, wherein there are one or more photosensitive surfaces of the same type corresponding to the preset wavelengths in the M photosensitive surfaces, wherein the photosensitive surfaces of the same type are used to collect and The first output light intensity and/or the second output light intensity corresponding to the preset wavelength, wherein the first output light intensity is the systolic light intensity, the second output light intensity is the diastolic light intensity, and the Similar photosensitive surfaces include one or more of said photosensitive surfaces;

The processing module is configured to determine the concentration of the measured tissue component according to the first output light intensity and the second output light intensity corresponding to the preset wavelength.
The device according to claim 76, wherein the M photosensitive surfaces have a first photosensitive surface of the same type and a second photosensitive surface of the same type corresponding to the preset wavelength, wherein the first photosensitive surface of the same type is used for The first output light intensity corresponding to the preset wavelength is collected, the second similar photosensitive surface is used to collect the second output light intensity corresponding to the preset wavelength, and the first similar photosensitive surface includes one or more each of the photosensitive surfaces, the second photosensitive surfaces of the same type include one or more of the photosensitive surfaces;

The processing module is configured to determine the concentration of the measured tissue component according to the first output light intensity and the second output light intensity corresponding to the preset wavelength.
129. The device of claim 129, wherein the first homogeneous photosensitive surface and the second homogeneous photosensitive surface are the same homogeneous photosensitive surface, and the first homogeneous photosensitive surface and the second homogeneous photosensitive surface receive The outgoing light is obtained by transmitting the incident light from different incident positions.
129. The device of claim 129, wherein the first homogeneous photosensitive surface and the second homogeneous photosensitive surface are different homogeneous photosensitive surfaces.
The device according to claim 129, wherein the average optical length of the outgoing light received by different photosensitive positions of each of the photosensitive surfaces of the first same type of photosensitive surfaces belongs to a first average optical length range, wherein the The first average optical path range is determined according to the first optical path average value, and the first optical path average value is calculated according to the average optical path length of the outgoing light received by each of the photosensitive positions of the first similar photosensitive surfaces the average obtained;

The average optical length of the outgoing light received by different photosensitive positions of each of the photosensitive surfaces of the second same type belongs to the second average optical path range, wherein the second average optical path range is based on the second light path. The second optical path average value is an average value calculated according to the average optical path length of the outgoing light received by each of the photosensitive positions of the second photosensitive surface of the same type.
132. The apparatus of claim 132, wherein the absolute value of the difference between the first optical path average value and the second optical path average value belongs to a first optical path difference range.
133. The device of claim 133, wherein the first average optical path range is less than or equal to the first optical path difference range and the second average optical path range is less than or equal to the first optical path difference range .
The apparatus of claim 133, wherein the first optical path difference range is determined according to an optimal differential optical path corresponding to the preset wavelength.
The device according to claim 129, wherein a source-detection distance of each of the photosensitive surfaces of the first same type of photosensitive surfaces corresponding to the preset wavelength from the center of the incident light is at a distance corresponding to the preset wavelength. The preset source detection distance range is determined according to the source detection distance between the floating reference position corresponding to the preset wavelength and the center of the incident light.
The device according to claim 76, wherein the M photosensitive surfaces have a same type of photosensitive surface corresponding to the preset wavelength, wherein the same type of photosensitive surface is used to collect a third photosensitive surface corresponding to the preset wavelength output light intensity, the same photosensitive surface includes one or more photosensitive surfaces;

The processing module is configured to determine the concentration of the measured tissue component according to the third output light intensity corresponding to the preset wavelength.
The device according to claim 137, wherein the difference between the average optical length of the outgoing light received by different photosensitive positions of each of the photosensitive surfaces of the same type of photosensitive surfaces and the optimal optical length corresponding to the preset wavelength The difference value belongs to the second optical path difference range.
The device of claim 76 or 77, wherein each of the photosensitive surfaces comprises an annular photosensitive surface or a non-annular photosensitive surface, and the shapes of the different photosensitive surfaces are the same or different.
139. The device of claim 139, wherein the non-annular photosensitive surface comprises a fan ring photosensitive surface, a circular photosensitive surface, a fan-shaped photosensitive surface, an elliptical photosensitive surface, or a polygonal photosensitive surface.
The device of claim 140, wherein the polygonal photosensitive surface comprises a square photosensitive surface, a rectangular photosensitive surface, or a triangular photosensitive surface.
139. The device of claim 139, wherein the homogeneous photosensitive surface comprises the annular photosensitive surface or the non-annular photosensitive surface, wherein the homogeneous photosensitive surface comprises one or more of the photosensitive surfaces, the homogeneous photosensitive surface The photosensitive surface is used to output one of the output light intensity.
The device of claim 142, wherein the photosensitive surface of the same type is the annular photosensitive surface, comprising:

In the case that the photosensitive surfaces of the same type include one photosensitive surface, the photosensitive surfaces of the same type are independent annular photosensitive surfaces;

When the photosensitive surfaces of the same type include a plurality of the photosensitive surfaces, the photosensitive surfaces of the same type are annular photosensitive surfaces formed according to the combination of the plurality of photosensitive surfaces;

The same type of photosensitive surface is the non-annular photosensitive surface, including:

In the case that the photosensitive surfaces of the same type include one photosensitive surface, the photosensitive surfaces of the same type are independent non-annular photosensitive surfaces;

In the case where the photosensitive surfaces of the same type include a plurality of the photosensitive surfaces, the photosensitive surfaces of the same type are non-annular photosensitive surfaces formed by combining the plurality of photosensitive surfaces.
The device according to claim 143, wherein, when it is determined that the distance between the photosensitive surfaces of the same type from the target site is greater than or equal to the second distance threshold, the photosensitive surfaces of the same type include a ring photosensitive surface, a fan ring photosensitive surface, a fan-shaped photosensitive surface, and a fan-shaped photosensitive surface. Photosensitive surface, round photosensitive surface or square photosensitive surface.
The device according to claim 143, wherein in the case that the distance between the same type of photosensitive surface and the target site is determined to be less than or equal to a third distance threshold, the shape of the same type of photosensitive surface is based on the emitted light Jitter distribution is determined.
145. The apparatus of claim 145, wherein the jitter distribution of the outgoing light comprises a decomposition into a jitter distribution in a first direction and a jitter distribution in a second direction, the first direction and the second direction Perpendicular to each other, the ratio of the length of the same type of photosensitive surface along the first direction to the length of the same type of photosensitive surface along the second direction is based on the jitter amplitude of the emitted light along the first direction and the Determined by the ratio of the shaking amplitudes of the outgoing light along the second direction, the shaking amplitude of the outgoing light along the first direction is the largest.
146. The device of claim 146, wherein the photosensitive surfaces of the same type include a rectangular photosensitive surface or an elliptical photosensitive surface, and the ratio of the length to the width of the rectangular photosensitive surface is determined according to the emitted light along the first direction Determined by the ratio of the jitter amplitude to the jitter amplitude of the outgoing light along the second direction, and the ratio of the long axis to the short axis of the elliptical photosensitive surface is based on the outgoing light along the first direction is determined by the ratio of the jitter amplitude to the jitter amplitude of the outgoing light along the second direction.
The device according to claim 76 or 77, wherein the anodes of different photosensitive surfaces in the M photosensitive surfaces are not electrically connected to each other, the anodes of some of the photosensitive surfaces are electrically connected, or the anodes of all the photosensitive surfaces are electrically connected.
An apparatus according to claim 76 or 77, wherein different parts of the same photosensitive surface are in the same plane or in different planes.
76 or 77, wherein the set of photosensitive surfaces are in the same plane or in different planes, wherein the set of photosensitive surfaces includes a plurality of photosensitive surfaces.
77. The apparatus of claim 76 or 77, wherein the preset wavelength is a wavelength sensitive to the measured tissue component.
The apparatus of claim 76 or 77, further comprising a temperature control module;

The temperature control module is used to control the temperature of the measurement region to remain within a preset temperature range during tissue composition measurement.
The device according to claim 76 or 77, further comprising a mask plate, the mask plate is arranged on the initial photosensitive surface, wherein the light transmittance of the mask plate is less than or equal to a light transmittance threshold;

The mask plate is used to obtain the photosensitive surface after disposing the mask plate on the initial photosensitive surface.
The apparatus of claim 153, wherein the shape of the mask is determined according to the shape of the jitter distribution of the outgoing light.
The device of claim 83, wherein a first sleeve is provided on the measurement probe;

The first end face of the first sleeve extends beyond the target surface of the measurement probe, wherein the first end face represents the end face close to the measurement area, and the target surface of the measurement probe represents the proximity to the measurement area s surface.
The device according to claim 155, wherein the second end surface and/or the inner area of the first sleeve are provided with scattering objects, wherein the first end surface and the second end surface are opposite end surfaces , the inner area includes part of the inner area or the entire inner area.
The device of claim 155 or 156, further comprising a second sleeve disposed outside a target area of the first sleeve, wherein the target area represents the first set The barrel extends over part or all of the target surface of the measurement probe.
157. The device of claim 157, wherein the second sleeve is provided with the diffuser.
156. The device of claim 155, wherein the inner diameter of the first sleeve is greater than or equal to an inner diameter threshold.
156. The device of claim 155, wherein the opening in the first end face of the first sleeve is greater than or equal to the opening in the second end face of the first sleeve.
The device of claim 76 or 77, wherein a refractive index matcher is filled between the photosensitive surface and the measurement area.
The device of claim 76 or 77, further comprising a protective portion;

The protection part is disposed on the target surface of the photosensitive surface, and is used to protect the photosensitive surface, wherein the target surface of the photosensitive surface represents a surface close to the measurement area.
A wearable device, comprising the tissue composition measurement device of any one of claims 76-162.
The wearable device according to claim 163, wherein the quality of the wearable device is less than or equal to a quality threshold, so that the movement law of the wearable device is consistent with the skin shaking law at the measurement area.
163. The wearable device of claim 163, wherein the wearable device causes the skin at the measurement area to have a movement magnitude less than or equal to a movement magnitude threshold.